Inductively heated multi-mode ultrasonic surgical tool

ABSTRACT

Thermal, electrosurgical and mechanical modalities may be combined in a surgical tool. Potentially damaging effects in a first modality may be minimized by using a secondary modality. In one example, thermal hemostasis may thus help electrosurgical applications avoid the adverse tissue effects associated with hemostatic monopolar electrosurgical waveforms while retaining the benefits of using monopolar incising waveforms.

RELATED APPLICATIONS

The present application claims the benefit of U.S. Provisional PatentApplication Ser. No. 61/170,203, filed Apr. 17, 2009, U.S. ProvisionalPatent Application Ser. No. 61/170,220, filed Apr. 17, 2009, and U.S.Provisional Patent Application Ser. No. 61/170,207, filed Apr. 17, 2009which are incorporated hereby by references in their entirety.

This application is part of a group of similar applications includingU.S. Patent application Ser. No. 12/647,340, filed Dec. 24, 2009,Attorney Docket Number 4340.NEXS.NP; U.S. patent application Ser. No.12/647,344, filed Dec. 24, 2009, Attorney Docket Number 4340.NEXS.NP2;U.S. patent application Ser. No. 12/647,350, filed Dec. 24, 2009,Attorney Docket Number 4340.NEXS.NP3; U.S. patent application Ser. No.12/647,355, filed Dec. 24, 2009, Attorney Docket Number 4340.NEXS.NP4;U.S. patent application Ser. No. 12/647,358, filed Dec. 24, 2009,Attorney Docket Number 4340.NEXS.NP5; U.S. patent application Ser. No.12/647,363, filed Dec. 24, 2009, Attorney Docket No. 4340.NEXS.NP6; U.S.patent application Ser. No. 12/647,371, filed Dec. 24, 2009, AttorneyDocket Number 4389.NEXS.NP; U.S. patent application Ser. No. 12/647,302filed Dec. 24, 2009, Attorney Docket Number 4389.NEXS.NP2; U.S. patentapplication Ser. No. 12/647,329, filed Dec. 24, 2009, Attorney DocketNumber 4390.NEXS.NP1; U.S. patent application Ser. No. 12/647,374, filedDec. 24, 2009, Attorney Docket Number 4390.NEXS.NP2; and U.S. patentapplication Ser. No. ______ filed Dec. 24, 2009, Attorney Docket Number4390.NEXS.NP4, each of which is incorporated hereby by references in itsentirety.

BACKGROUND OF THE INVENTION

1. The Field of the Invention

The present invention relates to surgical tools. More specifically, thepresent invention relates to thermally adjustable tools used in open andminimally invasive surgical procedures and interventional surgical andtherapeutic procedures.

2. State of the Art

Surgery generally involves cutting, repairing and/or removing tissue orother materials. These applications are generally performed by cuttingtissue, fusing tissue, or tissue destruction.

Current electrosurgery modalities used for cutting, coagulating,desiccating, ablating, or fulgurating tissue, have undesirable sideeffects and drawbacks.

Monopolar and bipolar electrosurgery modalities generally havedisadvantages relating to “beyond the tip” effects. These effects arecaused by passing alternating current through tissues in contact withconducting instruments or probes. One effect that that is believed to becaused by both modalities is electrical muscle stimulation, which mayinterrupt surgical procedures and require administration of musclerelaxants.

Monopolar surgical instruments require electric current to pass throughthe patient. A return electrode is placed on the patient, often on thepatient's thigh. Electricity is conducted from a “knife” electrodethrough the tissue and returns through the return electrode. Other formsof monopolar instruments exist, such as those which use the capacitiveeffect of the body to act as the return electrode or ground.

A low voltage high frequency waveform will incise, but has littlehemostatic effect. A high voltage waveform will cause adjacent tissuehemostasis and coagulation. Therefore, when hemostasis is desirable,high voltage is used. The high voltage spark frequently has deepertissue effects than the cut because the electricity must pass throughthe patient. The damage to the tissue extends away from the actual pointof coagulation. Furthermore, there are complaints of return electrodeburns. Yet, any reduction of voltage reduces the effectiveness ofhemostasis. Further, the temperature of the spark or arc cannot beprecisely controlled, which can lead to undesirable charring of targettissue.

Bipolar surgical instruments can produce tissue damage and problemssimilar to monopolar devices, such as sparking, charring, deeper tissueeffects and electric current damage away from the application of energywith varying effects due to the differing electrical conductivity oftissue types, such as nerve, muscle, fat and bone, and into adjacenttissues of the patient. However, the current is more, but notcompletely, contained between the bipolar electrodes. These electrodesare also generally more expensive because there are at least twoprecision electrodes that must be fabricated instead of the onemonopolar electrode.

Electrocautery resistive heating elements reduce the drawbacksassociated with charring and deeper tissue damage caused by otherelectrosurgery methods. However, such devices often present othertradeoffs, such as the latency in controlling heating and cooling time,and effective power delivery. Many resistive heating elements have slowheating and cooling times, which makes it difficult for the surgeon towork through or around tissue without causing incidental damage.

Tissue destruction instruments generally heat tissue to a predeterminedtemperature for a period of time to kill, or ablate, the tissue. In somecontrolled heating of tissues, a laser is directed to an absorptive capto reach and maintain a predetermined temperature for a predeterminedamount of time. While this provides the benefits of thermal heating, itis expensive due to the complexity and expense of laser hardware.

In another tissue destruction procedure, a microwave antenna array isinserted into the tissue. These arrays are powered by instruments thatcause microwave energy to enter and heat the tissue. While such devicesare often effective at killing, or ablating, the desired tissue, theyoften cause deeper tissue effects than the desired area. Additionallythe procedures can require expensive equipment.

Tissue destruction with resistively heated tools can produce unintendedcollateral tissue damage, in addition to having slow heating and coolingattributes.

Use of ferrite beads and alloy mixes in ceramics have been examined asalternatives. When excited by the magnetic field associated with highfrequency current passing through a conductor, ferrite beads and alloymixes in ceramics can reach high temperatures very quickly. However, onemajor problem with the use of these materials is that a largetemperature differential can cause the material to fracture, especiallywhen it comes into and out of contact with liquids. In other words, if ahot ferrite surgical instrument is quenched by a cooler pool of liquid,such as blood or other body fluids, the material's correspondingtemperature drops rapidly and may cause the material to fracture. Thesefractures not only cause the tool to lose its effectiveness as a heatsource, because the magnetic field is disrupted, but may requireextraction of the material from the patient. Obviously, the need toextract small pieces of ferrite product from a patient is highlyundesirable. Thus, there is a need for an improved thermal surgicaltool.

SUMMARY OF THE INVENTION

It is an object of the present invention to provide an improvedthermally adjustable surgical or therapeutic tool.

According to one aspect of the invention, a thermal surgical tool systemis provided with a ferromagnetic coating over a conductor and anoscillating electrical energy source for generating heat at the locationof the coating while generating an additional tissue effect through theuse of a second energy mode. The oscillating electrical energy may causeinductive heating of the ferromagnetic coating (the inductive thermalmode). Moreover, the surgeon may be able to quickly turn the inductivethermal mode of the surgical or therapeutic tool on and off due to asmall heat latency. This may provide the advantage of allowing thesurgeon to only deliver a thermal effect at desired locations, which mayalso prevent the accidental delivery of undesired thermal effects whilewaiting for the tool to cool. At the same time, a similar or differenttissue effect may be delivered simultaneously or in succession by thesecond mode. If similar, the use of both modes may cause an increase inefficiency. If different, the modes may complement each other such thatdrawbacks of a single mode may be reduced.

According to another aspect of the invention, a thermal surgical toolsystem may be configured so that the inductive thermal mode and/or asecond mode may be altered by the surgeon in near real-time to achievedifferent tissue effects, including hemostasis, tissue welding andtissue destruction.

According to another aspect of the invention, controlled thermal tissuedestruction may be performed by using the benefits of an inductivethermal mode combined with a second mode. The ferromagnetic coatedconductor can be used as part of a cutting, lesioning or ablating probewith the ferromagnetic coating providing thermal heating, as well as aconductive path for monopolar electrosurgical energy to pass in thetissue.

According to another aspect of the invention, the second mode mayinclude a monopolar or bipolar RF element, such as a monopolar orbipolar RF electrosurgical instrument, which may be used to cut andcoagulate tissue. While RF electrosurgical instruments are highlyeffective, they tend to create tissue damage beyond the incision whenused for sealing. Thus, an RF monopolar or bipolar electrosurgicalinstrument can be used in conjunction with a ferromagnetic coatedconductor which seals the tissue being cut with the RF instrument.

In accordance with yet another aspect of the present invention, themulti-mode surgical tool may include a thermal and ultrasonic tool forcutting and/or treating tissue.

These and other aspects of the present invention are realized in athermally adjustable surgical tool as shown and described in thefollowing figures and related description.

BRIEF DESCRIPTION OF THE DRAWINGS

Various embodiments of the present invention are shown and described inreference to the numbered drawings wherein:

FIG. 1 shows a perspective view of a thermal surgical tool system inaccordance with the principles of the present invention;

FIG. 2 shows a perspective view of an alternate embodiment of a thermalsurgical tool system in accordance with the present invention;

FIG. 3 shows a diagram of a thermal surgical tool system in accordancewith the principles of the present invention;

FIG. 4A shows a thermal surgical tool system with heat preventionterminals, heat sink, and wireless communication devices;

FIG. 4B shows a thermal surgical tool system with impedance matchingnetwork;

FIG. 5 shows a close-up, side cross-sectional view of a single layerferromagnetic coated conductor tip in accordance with one aspect of thepresent invention;

FIG. 6 shows a close-up, side cross-sectional view of a single layerferromagnetic coated conductor tip with a thermal insulator inaccordance with one aspect of the present invention;

FIG. 7A shows a close-up view of ferromagnetic coated conductor surgicaltool tip with a loop geometry in accordance with one aspect of thepresent invention;

FIG. 7B shows a close-up view of a ferromagnetic coated conductorsurgical tool tip with a generally square geometry in accordance withone aspect of the present invention;

FIG. 7C shows a close-up view of a ferromagnetic coated conductorsurgical tool tip with a pointed geometry;

FIG. 7D shows a close-up view of a ferromagnetic coated conductorsurgical tool tip with an asymmetrical loop geometry;

FIG. 7E shows a close-up view of a ferromagnetic coated conductorsurgical tool tip with a hook geometry in which the concave portion maybe used for therapeutic effect, including cutting;

FIG. 7F shows a close up view of a ferromagnetic coated conductorsurgical tool tip with a hook geometry in which the convex portion maybe used for therapeutic effect, including cutting;

FIG. 7G shows a close up view of a ferromagnetic coated conductorsurgical tool tip with an angled geometry;

FIG. 8 shows a cut-away view of a retracted snare;

FIG. 9A shows a side view of an extended snare;

FIG. 9B shows an alternate embodiment of an extended snare;

FIG. 10A shows a close-up view of a ferromagnetic coated conductorsurgical tool with a loop geometry and linear array of coatings;

FIG. 10B shows a close up view of a ferromagnetic coated conductorsurgical tool with an alternate hook geometry and linear array;

FIG. 11 shows a cut-away view of a retracted snare with an array ofcoatings;

FIG. 12 shows a side view of an extended snare with a linear array ofcoatings;

FIG. 13 shows an axial cross-sectional view of a single layerferromagnetic coated conductor surgical tool in the ferromagnetic-coatedregion;

FIG. 14A shows a perspective view of a multi-layer ferromagnetic coatedconductor surgical tool tip;

FIG. 14B shows a side cross-sectional view of a multi-layerferromagnetic coated conductor surgical tool tip shown in 14A;

FIG. 15 shows an axial cross-section of the multi-layer ferromagneticcoated conductor surgical tool tip shown in FIG. 14A;

FIG. 16 shows a cross-sectional view of a flattened side cylindricalgeometry ferromagnetic coated conductor showing electromagnetic lines offlux; in accordance with one aspect of the present invention;

FIG. 17 shows a closed conductor tip in accordance with another aspectof the present invention;

FIG. 18A shows a single edge ferromagnetic coated conductor surgical tipin accordance with one aspect of the invention;

FIG. 18B shows a double edge ferromagnetic coated conductor surgicaltip;

FIG. 18C shows a three wire ferromagnetic coated conductor surgical tip;

FIG. 18D shows a receptacle for the tips shown in FIGS. 18A through 18C;

FIG. 19A shows a normally cold cutting scalpel with alternate inductiveferromagnetic thermal function;

FIG. 19B shows an alternate embodiment of a normally cold cuttingscalpel with alternate inductive ferromagnetic thermal function;

FIG. 20A shows a thermal surgical tool with a spatula shaped geometry;

FIG. 20B shows a thermal surgical tool with a spatula shaped geometry ina forceps configuration;

FIG. 20C shows a top view of the thermal surgical tool of FIG. 20A withthe ferromagnetic coated conductor upon the primary geometry;

FIG. 20D shows a top view of the thermal surgical tool of FIG. 20A withthe ferromagnetic coated conductor embedded within the primary geometry;

FIG. 21A shows a thermal surgical tool with a ball shaped geometry andhorizontal winding;

FIG. 21B shows an alternate embodiment of a thermal surgical tool with aball shaped geometry and horseshoe configuration;

FIG. 21C shows an alternate embodiment of a thermal surgical tool with aball shaped geometry and vertical orientation;

FIG. 22A shows a thermal surgical tool with a pointed geometry;

FIG. 22B shows a thermal surgical tool with a pointed geometry in aforceps configuration;

FIG. 22C shows a thermal surgical tool having two different activatablethermal zones;

FIG. 23A shows a perspective view of a catheter having a coil offerromagnetic coated conductor disposed around the tip of the catheter;

FIG. 23B shows a perspective view of an ferromagnetic coated conductorsurgical catheter tip;

FIG. 24 shows a side view of an alternate embodiment of an ferromagneticcoated conductor surgical catheter tip;

FIG. 25 shows an alternate embodiment of a ferromagnetic coatedconductor surgical tip disposed within an endoscope;

FIG. 26 shows a tissue ablation tool;

FIG. 27 shows a multi-mode surgical tool with monopolar and thermalmodalities;

FIG. 28A shows a multi-mode tissue ablation tool within a metastasis intissue, such as in a liver;

FIG. 28B shows a close-up the ablating probe of FIG. 28A;

FIG. 28C shows a close-up of an ablating probe with a sensor;

FIG. 28D shows a close-up of a multiple tip ablating probe;

FIG. 29 shows a multi-mode surgical tool with bipolar and thermalmodalities;

FIG. 30 shows a side view of multi-mode forceps;

FIG. 31A shows a close up of an alternate embodiment of forceps tips;

FIG. 31B shows a diagram of a coated forceps tip;

FIG. 32A shows a multi-mode surgical tool with thermal and ultrasonicmodalities;

FIG. 32B shows a multi-mode surgical tool with thermal and ultrasonicmodalities with a hook primary geometry;

FIG. 32C shows a multi-mode surgical tool with thermal and ultrasonicmodalities with a sensor;

FIG. 32D shows a multi-mode surgical tool with thermal and ultrasonicmodalities with a second tip;

FIG. 33 shows a multi-mode surgical tool with thermal and ultrasonicmodalities with aspiration/irrigation and sensor; and.

FIG. 34 shows a thermal spectrum as related to tissue effects.

It will be appreciated that the drawings are illustrative and notlimiting of the scope of the invention which is defined by the appendedclaims. The embodiments shown accomplish various aspects and objects ofthe invention. It is appreciated that it is not possible to clearly showeach element and aspect of the invention in a single figure, and assuch, multiple figures are presented to separately illustrate thevarious details of the invention in greater clarity. Similarly, notevery embodiment need accomplish all advantages of the presentinvention.

DETAILED DESCRIPTION

The invention and accompanying drawings will now be discussed inreference to the numerals provided therein so as to enable one skilledin the art to practice the present invention. The drawings anddescriptions are exemplary of various aspects of the invention and arenot intended to narrow the scope of the appended claims.

As used herein, the term “ferromagnetic,” “ferromagnet,” and“ferromagnetism” refers to any ferromagnetic-like material that iscapable of producing heat via magnetic induction, including but notlimited to ferromagnets and ferrimagnets.

Turning now to FIG. 1, there is shown a perspective view of a thermalsurgical tool system, generally indicated at 10. As will be discussed inadditional detail below, the thermal tool system preferably uses aferromagnetic coated conductor to treat or destroy tissue (i.e.endothelial tissue welding, homeostasis, ablation, etc).

It will be appreciated that the thermal surgical tool uses heat toincise tissue and does not cut tissue in the sense of a sharp edge beingdrawn across the tissue as with a conventional scalpel. While theembodiments of the present invention could be made with a relativelysharp edge so as to form a cutting blade, such is not necessary as theheated coating discussed herein will separate tissue without the needfor a cutting blade or sharp edge. However, for convenience, the termcutting is used when discussing separating tissue.

In the embodiment shown as thermal surgical tool system 10, a controlmechanism, such as a foot pedal 20 is used to control output energyproduced by a power subsystem 30. The energy from the power subsystem 30may be sent via radio frequency (RF) or oscillating electrical energyalong a cable 40 to a handheld surgical tool 50, which contains aconductor 60 having a section thereof circumferentially coated with aferromagnetic coating 65. The ferromagnetic coating 65 may transfer theelectrical energy into available thermal energy via induction andcorresponding hysteresis losses in the ferromagnetic material disposedaround a conductor wire 66. (While conductor wire is used for ease ofreference, it will be appreciated that the conductor material need notbe a wire and those skilled in the art will be familiar with multipleconductors which will work in light of the disclosure of the presentinvention).

Application of a magnetic field (or magnetizing) to the ferromagneticcoating may produce an open loop B-H curve (also known as an openhysteresis loop), resulting in hysteresis losses and the resultantthermal energy. Electrodeposited films, such as a nickel-iron coatinglike PERMALLOY™, may form an array of randomly aligned microcrystals,resulting in randomly aligned domains, which together may have an openloop hysteresis curve when a high frequency current is passed throughthe conductor.

The RF energy may travel along the conductor's surface in a manner knownas the “skin effect”. The alternating RF current in the conductor'ssurface produces an alternating magnetic field, which may excite thedomains in the ferromagnetic coating 65. As the domains realign witheach oscillation of the current, hysteresis losses in the coating maycause inductive heating.

The RF conductor from the signal source up to and including the tip, mayform a resonant circuit at a specific frequency (also known as a tunedcircuit). Changes in the tip “detune” the circuit. Thus, should theferromagnetic coating 65 or the conductor wire 66 become damaged, thecircuit may likely become detuned. This detuning should reduce theefficiency of the heating of the ferromagnetic coating 65 such that thetemperature will be substantially reduced. The reduced temperatureshould ensure little or no tissue damage after breakage.

It should be understood that the handheld surgical tool 50 may includeindicia of the power being applied and may even include a mechanism forcontrolling the power. Thus, for example, a series of lights 52 could beused to indicate power level, or the handheld surgical tool 50 couldinclude a switch, rotary dial, set of buttons, touchpad or slide 54 thatcommunicates with the power source 30 to regulate power and therebyaffect the temperature at the ferromagnetic coating 65 to having varyingeffects on tissue. While the controls are shown on the foot pedal 20 orthe handheld surgical tool 50, they may also be included in the powersubsystem 30 or even a separate control instrument. Safety features suchas a button or touchpad that must be contacted to power the handheldsurgical tool 50 may be employed, and may include a dead man's switch.

While the ferromagnetic coating 65 heats through induction, it alsoprovides a temperature cap due to its Curie temperature. A Curietemperature is the temperature at which the material becomesparamagnetic, such that the alignment of each domain relative to themagnetic field decreases to such an extent that the magnetic propertiesof the coating are lost. When the material becomes paramagnetic, theheating caused by induction may be significantly reduced or even cease.This causes the temperature of the ferromagnetic material to stabilizearound the Curie temperature if sufficient power is provided to reachthe Curie temperature. Once the temperature has dropped below the Curietemperature, induction may again start causing heating of the materialup to the Curie temperature. Thus, the temperature in the ferromagneticcoating may reach the Curie temperature during inductive heating withthe application of sufficient power, but will not likely exceed theCurie temperature.

The thermal surgical tool system 10 allows the power output to beadjustable in order to adjust the temperature of the tool and its effecton tissue. This adjustability gives the surgeon precise control over theeffects that may be achieved by the handheld surgical tool 50. Tissueeffects such as cutting, hemostasis, tissue welding, tissue vaporizationand tissue carbonization occur at different temperatures. By using thefoot pedal 20 (or some other user control) to adjust the power output,the surgeon (or other physician, etc.) can adjust the power delivered tothe ferromagnetic coating 65 and consequently control the tissue effectsto achieve a desired result.

Thermal power delivery can be controlled by varying the amplitude,frequency or duty cycle of the alternating current waveform, oralteration of the circuit to affect the standing wave driving theferromagnetic coated conductor, which may be achieved by input receivedby the foot pedal 20, the power subsystem 30, or the controls on thehandheld surgical tool 50.

One additional advantage achieved by the inductive heating is that theferromagnetic material can be heated to a cutting temperature in a smallfraction of a second (typically as short one quarter of a second).Additionally, because of the relatively low mass of the coating, thesmall thermal mass of the conductor, and the localization of the heatingto a small region due to construction of the handheld surgical tool 50,the material will also cool extremely rapidly (i.e. approximately onehalf of a second). This provides a surgeon with a precise thermal toolwhile reducing accidental tissue damage caused by touching tissue whenthe thermal tool is not activated.

It will be appreciated that the time period required to heat and coolthe handheld surgical tool 50 will depend, in part, on the relativedimensions of the conductor 60 and the ferromagnetic coating 65 and theheat capacity of the structure of the surgical tool. For example, theabove time periods for heating and cooling of the handheld surgical tool50 can be achieved with a tungsten conductor having a diameter of about0.375 mm and a ferromagnetic coating of a Nickel Iron alloy (such asNIRON™ available from Enthone, Inc. of West Haven, Conn.) about thetungsten conductor about 0.0375 mm thick and two centimeters long.

One advantage of the present invention is that a sharp edge is notneeded. When power is not being supplied to the surgical tool, the toolwill not inadvertently cut tissue of the patient or of the surgeon if itis dropped or mishandled. If power is not being supplied to theconductor wire 66 and coating 65, the “cutting” portion of the tool maybe touched without risk of injury. This is in sharp contrast to acutting blade which may injure the patient or the surgeon if mishandled.

Other additions may also be placed on the handpiece in variouslocations. This may include a sensor stem 12 including a sensor toreport temperature or a light to illuminate the surgical area.

Turning now to FIG. 2, a perspective view of an alternate embodiment ofa thermal surgical system 10 is shown. In FIG. 2, the power source 30 iscontained within the foot pedal 20. Depending on the application andpower required, the instrument may even be entirely battery powered forrelatively low power applications. An alternate embodiment for low powerrequirements may include the battery, power adjustment and powerdelivery, all self-contained in the handle 51 of the handheld surgicaltool 50. Furthermore, a wireless communication module can be employed tosend and receive information from the handheld surgical tool 50,including status and control settings that would enable users to monitorsystem performance and alter power settings remotely from the handheldsurgical tool 50 itself.

It is our understanding that this thermal solution may provideadvantages over monopolar and bipolar electrical systems currentlyavailable because the thermal damage may remain very close to theferromagnetic surface of the coated region, whereas monopolar andbipolar electrical tissue ablation may frequently cause tissue damagefor a distance away from the point of contact. It is our understandingthat this method may also overcome disadvantages of other thermaldevices based upon resistive heating, which may require more time toheat and cool, and thus present greater patient risk, while potentiallyhaving higher voltage requirements at the point of heating.

Furthermore, the thin ferromagnetic coating 65, disposed along a smallsegment of the conductor, may reduce the heating of other non-targetmaterial in the body, such as blood when working within the heart inatrial ablation—which can lead to complications if a clot is formed. Thesmall thermal mass of the conductor wire 66, and localization of theheating to a small region provided by the construction of the tool (i.e.ferromagnetic coating 65 and adjacent structures) provides a reducedthermal path for heat transfer in directions away from the location ofthe ferromagnetic coating 65. This reduced thermal path may result inthe precise application of heat at only the point desired. As thistechnology alone does not employ a spark or an arc like monopolar orbipolar technology, risks of ignition, such as by anesthetic gasseswithin or around the patient by sparks, are also reduced.

The thermal surgical tool system 10 may be used for a variety oftherapeutic means—including sealing, “cutting” or separating tissue,coagulation, or vaporization of tissue. In one configuration, thethermal surgical tool system 10 may be used like a knife or sealer,wherein the surgeon is actively “cutting” or sealing tissue by movementof the ferromagnetic coating 65 through tissue. The thermal action ofthe embodiments disclosed here may have distinct advantages includingsubstantial reduction, if not elimination, of deep tissue effectscompared with those associated with monopolar and bipolar RF energydevices.

In another configuration, the ferromagnetic coated conductor 60 may beinserted into a lesion and set to a specific power delivery or variablepower delivery based on monitored temperature. The thermal effects onthe lesion and surrounding tissue may be monitored until the desiredthermal effect is achieved or undesired effects are noticed. Oneadvantage of the application of the ferromagnetic coated conductor isthat it may be cost-effective compared to microwave or thermal lasermodalities and avoids the undesired tissue effects of microwave lesiondestruction. Thus, for example, a surgeon can insert the ferromagneticcoated conductor into a tumor or other tissue to be destroyed andprecisely control the tissue damage that is created by activating thehandheld surgical tool 50.

Sensors may be used to monitor conditions of the handheld surgical tool50 or the tissue, such as an infrared detector or sensor stem 12. Forinstance, the temperature of the device or tissue may be important inperforming a procedure. A sensor in the form of a thermocouple, ajunction of dissimilar metals, thermistor or other temperature sensormay detect the temperature at or near the ferromagnetic coating 65 ortissue. The sensor may be part of the device, such as a thermocoupleplaced as a part of the conductor or near the ferromagnetic coating, orseparate from the handheld surgical tool 50, such as a separate tipplaced near the tissue or ferromagnetic coating 65. The temperatures mayalso be correlated with tissue effects, seen in FIG. 27. Other usefulconditions to monitor may include, but are not limited to, color,spectral absorption, spectral reflection, temperature range, watercontent, proximity, tissue type, transferred heat, tissue status,impedance, resistance, voltage and visual feedback (i.e. a camera,fiberoptic or other visualization device).

The handheld surgical tool 50 may be configured for repeat sterilizationor single patient uses. More complex devices may be useful for repeatsterilization, while more simple devices may be more useful for singlepatient use.

A method for treating or cutting tissue may include the steps of:selecting a surgical tool having a cutting edge and a conductor disposedadjacent the cutting edge, at least a portion of which is coated with aferromagnetic material; cutting tissue with the cutting edge; andapplying oscillating electrical energy to the conductor to heat theferromagnetic material and thereby treating the cut tissue.

Optional steps of the method may include the steps of: causinghemostasis within the cut tissue; using the heated ferromagneticmaterial to incise tissue; or using the heated ferromagnetic material tocause vascular endothelial welding.

Referring now to FIG. 3, a diagram of an embodiment of the adjustablethermal surgical tool system 10 is shown. The power delivery to theferromagnetic coating 65 is controlled by a modulated high frequencywaveform. The modulated waveform allows power delivery to be controlledin a manner that adjustably modifies, allows or blocks portions of thewaveform based on the desired power delivery.

In FIG. 3, an initial waveform 110 is passed through a modulator 120receiving commands from a foot pedal 20. The waveform is created by anoscillator 130 to the desired frequency, and modulated by the modulator120, which may include, but is not limited to, one or more of amplitude,frequency or duty cycle modulation, including a combination thereof. Theresultant signal is then amplified by an amplifier 140. The amplifiedsignal is sent across a tuned cable 150, meaning that the cable is tunedto provide a standing wave with maximum current and minimum voltage atthe location of the ferromagnetic coating 65 of the handheld surgicaltool 50. Alternatively, the cable 150 may not be tuned, but a circuitmay be placed in the handle 51 to impedance match the ferromagneticcoated conductor 60 as a load to the power source 30.

The thermal surgical tool system 10 may be tuned by specifying thelocation of the ferromagnetic coating 65 with respect to the amplifier140 (such as cable length) and tuning the high frequency signal toapproximately a resonant standing wave such that current is maximized atthe location of the ferromagnetic coating 65.

It should be recognized that the surgical tool may operate in a dynamicenvironment. Thus when used herein, approximately a standing wave meansthat a circuit may be tuned such that the signal may be near an optimalstanding wave but may not achieve it, may only achieve the wave forsmall amounts of time, or may successfully achieve a standing wave forlonger periods of time. Similarly, any use of “standing wave” withoutthe modifier of approximate should be understood to be approximate inthe context of the thermal surgical tool.

One method for achieving such current maximization is to connect theferromagnetic coated conductor 60 to a cable 150 that is an odd multipleof one-quarter wavelengths in length and connected to the output of theamplifier 140. The design of the circuit having a resonant standing waveis intended to optimize power delivery to the ferromagnetic coating.However, in one embodiment, the power source 30 could be positioned atthe location of (or closely adjacent to) the ferromagnetic coating 65,and tuning could be achieved with electrical components, all within asingle handheld, battery-powered instrument. Alternatively, electricalcomponents necessary for impedance matching can be located at the outputstage of the amplifier 140. Further, electrical components, such as acapacitor or inductor, can be connected in parallel or series to theferromagnetic coated conductor 60 at the location of the connection ofthe conductor wire 66 to the cable 150, in order to complete a resonantcircuit.

Dynamic load issues can be caused by the interaction of theferromagnetic coated conductor 60 with various tissues. These issues maybe minimized by the standing current wave being maximized at the loadlocation. Multiple different frequencies can be used, includingfrequencies from 5 megahertz to 24 gigahertz, preferably between 40 MHzand 928 MHz. In some regulated countries it may be preferable choosefrequencies in the ISM bands such as bands with the center frequenciesof 6.78 MHz, 13.56 MHz, 27.12 MHz, 40.68 MHz, 433.92 MHz, 915 MHz, 2.45GHz, 5.80 GHz, 24.125 GHz, 61.25 GHz, 122.5 GHz, 245 GHz. In oneembodiment, the oscillator 130 uses an ISM Band frequency of 40.68 MHz,a class E amplifier 140, and a length of coaxial cable 150, all of whichmay be optimized for power delivery to a ferromagnetic coated tungstenconductor 60 with a ferromagnetic coating 65 consisting of a thicknessof between 0.05 micrometer and 500 micrometers, and preferably between 1micrometer and 50 micrometers. A useful estimate may be to start theferromagnetic coating thickness at 10% of the conductor diameter, and upto 5 cm long. However, the ferromagnetic coating may be disposed as faralong the length or along multiple regions of the conductor as whereheating may be desired. (The ferromagnetic coating 65 may be formed froma Nickel Iron (NiFe) alloy, such as NIRON™ from Enthone, Inc. of WestHaven, Conn., or other ferromagnetic coatings, including Co, Fe,FeOFe₂O₃, NiOFe₂O₃, CuOFe₂O₃, MgOFe₂O₃, MnBi, Ni, MnSb, MnOFe₂O₃,Y₃Fe₅O₁₂, CrO₂, MnAs, Gd, Dy, EuO, magnetite, yttrium iron garnet,aluminum, PERMALLOY™, and zinc.)

The size of the conductor, size of the ferromagnetic coating, associatedthicknesses, shape, primary geometry, composition, power supply andother attributes may be selected based on the type of procedure andsurgeon preferences. For example, a brain surgeon may desire a smallinstrument in light handheld package designed for quick applicationwithin the brain, while an orthopedic surgeon may require a largerdevice with more available power for operation on muscle.

The conductor may be formed from copper, tungsten, titanium, stainlesssteel, platinum and other materials that may conduct electricity.Considerations for the conductor may include, but are not limited tomechanical strength, thermal expansion, thermal conductivity, electricalconduction/resistivity, rigidity, and flexibility. It may be desirableto form the conductor wire 66 of more than one material. Connection oftwo dissimilar metals may form a thermocouple. If the thermocouple wereplaced in the vicinity or within of the ferromagnetic coating, thethermocouple provides a temperature feedback mechanism for the device.Further, some conductors may have a resistivity that correlates totemperature, which may also be used to measure temperature.

The tuning of the power source 30 also reduces the amount of highfrequency energy radiating into the patient to near zero, as voltage islow, and ideally zero, at the location of the ferromagnetic coating 65.This is in contrast to monopolar devices, which require a grounding padto be applied to the patient, or bipolar devices, both of which passcurrent through the tissue itself. The disadvantages of these effectsare well known in the literature.

In many of these embodiments discussed herein, the combination of cablelength, frequency, capacitance and inductance may also be used to adjustefficiency and tool geometry by tuning the power source 30 to delivermaximum power to the ferromagnetic coating 65, and therefore, maximumheat to the tissue. A tuned system also provides for inherent safetybenefits; if the conductor were to be damaged, the system would becomedetuned, causing the power delivery efficiency to drop, and may evenshut down if monitored by an appropriate safety circuit.

The amount of power delivered to the patient tissue may be modified byseveral means to provide precise control of tissue effects. The powersource 30 may incorporate a modulator 120 for power delivery asdescribed above. Another embodiment uses modification of the magneticfield by altering the geometry of the conductor wire 66 and theferromagnetic coating 65 through which it passes, such as would becaused by a magnet. Placement of the magnet nearby the ferromagneticcoating 65 would similarly alter the induction effect and thereby changethe thermal effect.

While modulation has been discussed as a method to control powerdelivery, other methods may be used to control power delivery. In oneembodiment, the output power, and correspondingly the temperature, ofthe tool is controlled by tuning or detuning the drive circuit,including the conductor wire 66 and ferromagnetic coated conductor 60.

Turning now to FIG. 4A, a thermal surgical tool system 10 withconnectors which attach to opposing first and second ends of a wireconductor is shown. The conductors as shown in FIG. 4A may be formed byheat prevention terminals 280, such as crimp connectors that providethermal isolation. One or more heat sinks 282, and wirelesscommunication devices 286 may also be included. The wire conductor 220may be connected to the handheld surgical tool 50 by terminals 280and/or a heat sink 282 at opposing first and second ends of theconductor. Portions of the conductor may extend into the handle intoterminals, while the ferromagnetic coating portion of the conductor mayextend beyond the handle. The terminals 280 may have a poor thermalconductance such that the terminals 280 reduce the heat transfer fromthe conductor into the handheld surgical tool 50. In contrast, the heatsink 282 may draw any residual heat from the terminals 280 and dissipatethe heat into other mediums, including the air. Connectors andconnections may also be achieved by wire bonding, spot and otherwelding, in addition to crimping.

Preventing thermal spread may be desirable because the other heatedportions of the handheld surgical tool 50 may cause undesired burns,even to the operator of the handheld surgical tool 50. In oneembodiment, terminals 280 are used to conduct the electric current, butprevent or reduce thermal conduction beyond the ferromagnetic coatedconductor.

The thermal surgical tool may also communicate wirelessly. In oneembodiment, the user interface for monitoring and adjusting power levelsmay be housed in a remote, wirelessly coupled device 284. The wirelesslycoupled device may communicate with a wireless module 286 containedwithin the thermal surgical tool system 10, including the handheldsurgical tool 50, the control system (such as foot pedal 20), and/or thepower subsystem 30. By housing the control interface and display in aseparate device, the cost of the handheld surgical tool 50 portion maybe decreased. Similarly, the external device may be equipped with moreprocessing power, storage and, consequently, better control and dataanalysis algorithms.

Turning now to FIG. 4B, a thermal surgical tool system with impedancematching network is shown. The impedance matching network may match theoutput impedance of the signal source to the input impedance of theload. This impedance matching may aid in maximizing power and minimizingreflections from the load.

In one embodiment, the impedance matching network may be a balun 281.This may aid in power transfer as the balun 281 may match the impedanceof the ferromagnetic coated conductor terminals 287 to the amplifiercable terminals 283 (shown here as a coaxial cable connection). In sucha configuration, some baluns may be able to act as a heat sink andprovide thermal isolation to prevent thermal spread from the thermalenergy at the ferromagnetic coating 65 transferred by the wire conductor220 to terminals 287. The appropriate matching circuitry may also beplaced on a ceramic substrate to further sink heat away or isolate heataway from the rest of the system, depending on the composition of thesubstrate.

It should be recognized that these elements discussed in FIGS. 4A and 4Bcan be used in conjunction with any of the embodiments shown herein.

Turning now to FIG. 5, a longitudinal cross section of the ferromagneticcoated conductor is shown. As an alternating current 67 is passedthrough conductor 66, a time varying magnetic field 68 is induced aroundconductor 66. The time varying magnetic field 68 is resisted by theferromagnetic coating 65, causing the ferromagnetic coating 65 todissipate the inductive resistance to the time varying magnetic field 68as heat. Should the ferromagnetic coating 65 reach it's Curie point, themagnetic resistive properties of ferromagnetic coating 65 becomesubstantially reduced, resulting in substantially decreased resistanceto time varying magnetic field 68. As there is very little mass to theferromagnetic coating 65, the magnetic field causes the ferromagneticcoating 65 to quickly heat. Similarly, the ferromagnetic coating 65 issmall in mass compared to conductor 66 and therefore heat will quicklydissipate therefrom due to thermal transfer from the hot ferromagneticcoating 65 to the cooler and larger conductor 66, as well as from theferromagnetic coating 65 to the surrounding environment.

It should be appreciated that while the figures show a solid circularcross-section, the conductor cross-section may have various geometries.For instance, the conductor may be a hollow tubing such that it reducesthermal mass. Whether solid or hollow, the conductor may also be shapedsuch that it has an oval, triangular, square or rectangularcross-section.

As is also evident from FIG. 5, the ferromagnetic coating may be betweena first section (or proximal portion) and a second section (or distalportion) of the conductor. This may provide the advantage of limitingthe active heating to a small area, instead of the entire conductor. Apower supply may also connect to the first and second section to includethe ferromagnetic coating within a circuit providing power.

A method of using the surgical tool may include the steps of: selectinga conductor and plating a ferromagnetic coating upon the conductor.

Optional steps to the method may include: selecting a size of aconductor having a ferromagnetic coating disposed on a portion thereofaccording to a desired procedure; selecting a thermal mass of aconductor having a ferromagnetic coating disposed on a portion thereofaccording to a desired procedure; selecting a conductor from the groupof loop, solid loop, square, pointed, hook and angled; configuring theoscillating electrical signal to heat the coating to between 37 and 600degrees Centigrade; configuring the oscillating electrical signal toheat the coating to between 40 and 500 degrees Centigrade; causing thecoating to heat to between about 58-62 degrees Centigrade to causevascular endothelial welding; causing the coating to heat to betweenabout 70-80 degrees Centigrade to promote tissue hemostasis; causing thecoating to heat to between about 80-200 degrees Centigrade to promotetissue searing and sealing; causing the coating to heat to between about200-400 degrees Centigrade to create tissue incisions; or causing thecoating to heat to between about 400-500 degrees Centigrade to causetissue ablation and vaporization. Treatment may include incising tissue,causing hemostasis, ablating tissue, or vascular endothelial welding.

Turning now to FIG. 6, a close-up, longitudinal cross-sectional view ofa single layer cutting tip with a thermal insulator 310 is shown. Alayer of thermal insulator 310 may be placed between the ferromagneticcoating 65 and the conductor 66. Putting a layer of thermal insulator310 may aid in the quick heating and cool-down (also known as thermalresponse time) of the tool by reducing the thermal mass by limiting theheat transfer to the conductor 66.

The thickness and composition of the thermal insulator may be adjustedto change the power delivery and thermal response time characteristicsto a desired application. A thicker coating of thermal insulator 310 maybetter insulate the conductor 66 from the ferromagnetic coating 65, butmay require an increased power compared with a thinner coating ofthermal insulator 310 in order to induce a magnetic field sufficient tocause the ferromagnetic coating to heat.

In the embodiments shown in FIGS. 7A-7G a plurality of embodiments areshown in which the surgical tip 210 is a tool which includes a wireconductor 220 which has a portion of its length coated with a relativelythin layer of ferromagnetic coating 65. As shown in FIGS. 7A-7G, theferromagnetic coating 65 may be a circumferential coating around a wireconductor 220. When the wire conductor 220 is excited by a highfrequency oscillator, the ferromagnetic coating 65 will heat throughinduction according to the power delivered, with an absolute limitprovided by its Curie temperature. Because of the small thickness offerromagnetic coating 65 and the tuned efficiency of high frequencyelectrical conduction of the wire at the position of the ferromagneticcoating 65, the ferromagnetic coating 65 will heat very quickly (i.e. asmall fraction of a second) when the current is directed through thewire conductor 220, and cool down quickly (i.e. a fraction of a second)when the current is stopped.

Turning now to FIGS. 7A, 7B, 7C, 7D, 7E, 7F AND 7G, ferromagnetic coatedconductor surgical tips 210 a, 210 b, 210 c, 210 d, 210 e, 210 f and 210g are shown. In each of these embodiments, a portion of wire conductor220 is bent and coated with a ferromagnetic coating 65 such that theferromagnetic coating 65 is only exposed to tissue where the desiredheating is to occur. FIGS. 7A and 7B are loop shapes that can be usedfor tissue cutting or excision, depending upon the orientation of thetool to the tissue. FIG. 7A shows a rounded geometry, while FIG. 7Bshows a squared geometry. FIG. 7C shows a pointed geometry for heatedtip applications that can be made very small because the process oftissue dissection, ablation, and hemostasis requires only a smallcontact point. FIG. 7D shows an asymmetric tool with a loop geometry,where the ferromagnetic coating 65 is only disposed on one side of thetool. FIG. 7E shows a hook geometry where the ferromagnetic coating 65is disposed on the concave portion of the hook. FIG. 7F shows a hookgeometry where the ferromagnetic coating 65 is disposed on the convexportion of the hook. FIG. 7G shows an angled geometry, which may be usedin similar situations as a scalpel. Use of these various geometries offerromagnetic coating 65 upon a wire conductor 220 may allow thesurgical tip to act very precisely when active and to be atraumatic whennon-active.

In one representative embodiment, the electrical conductor may have adiameter of 0.01 millimeter to 1 millimeter and preferably 0.125 to 0.5millimeters. The electrical conductor may be tungsten, copper, othermetals and conductive non-metals, or a combination such as twodissimilar metals joined to also form a thermocouple for temperaturemeasurement. The electrical conductor may also be a thin coating ofconductor, such as copper, dispersed around a non-metallic rod, fiber ortube, such as glass or high-temperature plastic, and the conductivematerial, in-turn, may be coated with a thin layer of ferromagneticmaterial. The magnetic film forms a closed magnetic path around theelectrically conductive wire. The thin magnetic film may have athickness about 0.01-50% and preferably about 0.1% to 20% of thecross-sectional diameter of the wire. Due to the close proximity of thecoating to the wire, a small current can produce high magnetic fields inthe coating and result in significant temperatures. Since the magneticpermeability of this film is high and it is tightly coupled to theelectrical conductor, low levels of current can result in significanthysteresis losses.

It is therefore possible to operate at high frequencies with lowalternating current levels to achieve rapid inductive heating up to theCurie point. The same minimal thermal mass allows rapid decay of heatinto tissue and/or the conductor with cessation of current. The tool,having low thermal mass, provides a rapid means for temperatureregulation across a therapeutic range between about 37 degrees Celsiusand 600 degrees Celsius, and preferably between 40 and 500 degreesCelsius.

While Curie point has been previously described as a temperature cap,instead, here a material with a Curie point beyond the anticipatedtherapeutic need may be selected and the temperature can be regulatedbelow the Curie point.

While some tip geometries are shown in FIGS. 7A through 7G, it isanticipated that multiple different geometries of the ferromagneticcoated conductor 60 may be used.

Turning now to FIG. 8, a cut-away view of a snare 350 in a retractedposition is shown. A ferromagnetic coating is placed on a conductor toform a snare loop 355 and then placed within a sheath 360. Whileretracted, the snare loop 355 may rest within a sheath 360 (or someother applicator, including a tube, ring or other geometry designed toreduce the width of the snare when retracted). The sheath 360 compressesthe snare loop 355 within its hollow body. The sheath 360 may then beinserted into a cavity where the target tissue may be present. Once thesheath 360 reaches the desired location, the snare loop 355 may beextended outside the sheath 360, and end up deployed similar to FIG. 9A.In one embodiment, the conductor 365 may pushed or pulled to causeextension and retraction of the snare loop 355.

Turning now to FIG. 9A a side view of a snare 350 in an extendedposition is shown. Once extended, the snare 355 loop may be used inseveral different ways. In one embodiment, the snare loop 355 may beplaced substantially around the target tissue, such that the tissue iswithin the snare loop 355. The ferromagnetic coating may then be causedto be inductively heated as discussed above. The snare loop 355 is thenretracted back into the sheath 360 such that the target tissue isseparated and removed from tissue adjacent the target tissue. Thedesired temperature range or power level may be selected for hemostasis,increased tissue separation effectiveness or other desired setting. Forexample, in one embodiment, the snare 350 is configured for nasal cavitypolyp removal.

In another use, the snare 350 may be configured for tissue destruction.Once within the desired cavity, the snare may be extended such that aportion of the snare loop 355 touches the target tissue. The snare loop355 may then be inductively heated such that a desired tissue effectoccurs. For example, in one embodiment, the sheath may be placed near orin the heart and the snare loop 355 inductively heated to cause aninterruption of abnormal areas of conduction in the heart, such as inatrial ablation.

Turning now to FIG. 9B, an alternate embodiment of a snare 351 is shown.The applicator may be a ring 361 instead of a sheath as in FIG. 9A.Similar to the sheath, the ring 361 may be used to force the loop intoan elongated position. Various devices could be used to hold the ring inplace during use.

A method of separating tissue may include the steps of: selecting aconductor having a ferromagnetic coating disposed on a portion thereof;placing the portion of the conductor having the ferromagnetic coatingwithin a tube; inserting the tube into a cavity; deploying the portionof the conductor having the ferromagnetic coating within the cavity; anddelivering an oscillating electrical signal to the conductor so as toheat the ferromagnetic coating while the heated ferromagnetic coating isin contact with a target tissue.

Optional steps may include: deploying step further comprises placing theferromagnetic coating substantially around the target tissue; retractingthe ferromagnetic coating portion of the conductor into the tube;causing hemostasis in the target tissue; forming the conductor into abent geometry such that a portion of the conductor remains within thetube; and touching a ferromagnetic covered portion of the bent geometryto the target tissue.

A method of removing tissue may include the steps of: selecting aconductor having at least one portion having a ferromagnetic conductordisposed thereon; and placing the ferromagnetic conductor around atleast a portion of the tissue and pulling the ferromagnetic conductorinto contact with the tissue so that the ferromagnetic conductor cutsthe tissue.

Optional steps may include: using a conductor having a plurality offerromagnetic conductors in an array or passing an oscillatingelectrical signal through the conductor while the ferromagnetic materialis in contact with the tissue.

Turning now to FIG. 10A, a close-up view of a cutting tip with a loopgeometry and linear array of coatings is shown. While the aboveembodiments have disclosed a continuous ferromagnetic coating on aconductor, in another embodiment, there are more than one coatingseparated by gaps on a single conductor. This is termed a linear arrayof ferromagnetic elements (an example of a parallel array offerromagnetic elements can be seen in FIGS. 18A-18C).

In one embodiment, a loop geometry 270 a may have multiple ferromagneticcoatings 65, 65′, and 65″ which are separated by gaps on a wireconductor 220. In another embodiment shown in FIG. 10B, a close up viewof a cutting tip with an alternate hook geometry 270 b and linear arrayof ferromagnetic coatings 65 and 65′ is shown on a wire conductor 220.The linear array may include the advantage of allowing flexibility inbuilding a desired thermal geometry.

The conductor 220 which may be formed of an alloy having shape memory,such as Nitinol (nickel titanium alloy). A Nitinol or other shape memoryalloy conductor can be bent into one shape at one temperature, and thenreturn to its original shape when heated above is transformationtemperature. Thus, a physician could deform it for a particular use at alower temperature and then use the ferromagnetic coating to heat theconductor to return it to its original configuration. For example, ashape memory alloy conductor could be used to form snare which changesshape when heated. Likewise, a serpentine shape conductor can be made ofNitinol or other shape memory alloy to have one shape during use at agiven temperature and a second shape at a higher temperature. Anotherexample would be for a conductor which would change shape when heated toexpel itself from a catheter or endoscope, and then enable retractionwhen cooled.

In another embodiment, the ferromagnetic coatings may be formed in sucha way that an individual coating among the linear array may receive morepower by tuning the oscillating electrical energy. The tuning may beaccomplished by adjusting the frequency and/or load matching performedby the power source to specific ferromagnetic coatings.

Turning now to FIG. 11, a cut-away view of a snare tool 370 with alinear array of coatings in a retracted position is shown. In someembodiments, some ferromagnetic coatings may lack the elasticity toeffectively bend into a retracted position. Therefore, individualcoating segments 375 may be separated by gaps 380 such that theconductor 365 may be flexed while the coating segments 375 may remainrigid.

Similarly, the snare tool 370 may be extended, as seen in FIG. 12. Thegaps 380 between the coating segments 375 may be adjusted such that theheating effect will be similar in the gaps 380 as the coating segments.Thus, the snare tool 370 with linear array may act similar to the snarewith flexible coating in FIGS. 8 and 9.

Turning now to FIG. 13, a cross-sectional view of a single layer cuttingtip in the ferromagnetic-coated region is shown. The ferromagneticcoating 65 is disposed over a wire conductor 220. The ferromagneticcoating 65 provides several advantages. First, the ferromagnetic coating65 is less fragile when subjected to thermal stress than ferrite beads,which have a tendency to crack when heated and then immersed in liquid.The ferromagnetic coated conductor 60 has been observed to surviverepeated liquid immersion without damage. Further, the ferromagneticcoating 65 has a quick heating and quick cooling quality. This is likelybecause of the small amount of ferromagnetic coating 65 that is actedupon by the magnetic field, such that the power is concentrated over asmall area. The quick cooling is likely because of the small amount ofthermal mass that is active during the heating. Also, the composition ofthe ferromagnetic coating 65 may be altered to achieve a different Curietemperature, which would provide a maximum self-limiting thermal ceilingattribute to the device.

Turning now to FIGS. 14A, 14B and 15, a multilayer surgical tool tip isshown. A cross section of 14A along the 221 line may result in FIG. 14Bwhich shows alternating layers of wire conductor 220 and 220′ andferromagnetic coating 65 and 65′. Heating capacity may be increased bylayering thin layers of alternating conductor 220 and 220′ material andferromagnetic coating 65 and 65′, while still maintaining quick heatingand cooling advantages. FIG. 15 shows an axial cross-sectional view fromFIG. 14A along the 390 line. The alternating layers of conductor 220 and220′, and ferromagnetic coating 65 and 65′ may also be seen.

Turning now to FIG. 16, a flattened side cylindrical geometry is shown.The flat surface 180 can be manufactured to cause a thin plating 182 offerromagnetic coating on the conductor 66 relative to the thickerplating around the rest of the conductor 66. This thin plating 182 mayresult in selective first onset heating in this flat surface 180.Inductive heating may be proportional to flux density within themagnetically permeable coating. In one embodiment, an asymmetricallythinned coating has a small cross sectional thickness and may generatehigher hysteresis losses in the form of heat. Thus, a therapeutictemperature may be achieved with yet lower power at the flat surface 180with higher flux density 192 compared to a cooler opposite side with adiminished flux density 190. An advantage is that fast temporal responseand distributed optimal heating at the tissue interface may be enhanced.

Turning now to FIG. 17, the ferromagnetic coating 65 may also beconfigured to focus the temperature increase on the outside of theferromagnetic coating 65, further reducing the time needed to cool theferromagnetic coating 65 in a relatively high power application. Anexample of such a configuration is shown in FIG. 17, wherein the fieldsgenerated by the current flow 230 and 230′ (the arrows) may have acancelling effect with respect to each other within the ferromagneticcoating 65 surrounding both conductors, keeping the ferromagneticmaterial between the looped conductor 441 cooler than the ferromagneticmaterial at the perimeter.

Turning now to FIGS. 18A-18D, several surgical tip 194 geometries aredemonstrated. In FIG. 18A, a surgical tip 194 a with a single smalldiameter electrically conductive wire plated with the thin film magneticmaterial 196 is shown. In FIG. 18B, the surgical tip 194 b with twosmall diameter electrically conductive wires plated with the thin filmmagnetic material 196′ is shown. In FIG. 18C, a surgical tip 194 c withthree small diameter electrically conductive wires plated with the thinfilm magnetic material 196″ are shown. It is thus contemplated that atip geometry may consist of a plurality of small diameter electricallyconductive wires plated with the thin film magnetic material. Such adesign maintains the temporal heat responsiveness (rapid onset, rapidoffset) essential to the dynamic surgical environment due to minimalmass of the ferromagnetic coated conductor. It is thus possible toconfigure a flat tine with two or more spaced wires as a practicalmonothermal or multithermal tool. Further, the tips 194 a, 194 b and 194c may also be exchangeable as seen in FIG. 18D, which has a receptacle198 for the tips 194 in FIGS. 18A-18C. It will be appreciated that thegenerator system may be configured to adjust the power jointly deliveredto two or more of the conductors and that a user control (as shown inother figures) can be provided for that purpose.

The ferromagnetic coating 65 can be used to contact the tissue directly,or, a non-stick coating, such as TEFLON (PTFE), or similar material,could be applied over the ferromagnetic coating and conductor to preventsticking to the tissue. Alternatively, the ferromagnetic coating couldbe coated with another material, such as gold, to improvebiocompatibility, and/or polished, to reduce drag force when drawingthrough tissue. The ferromagnetic coating could also be coated by athermally-conductive material to improve heat transfer. In fact, asingle coating may be selected to have multiple desirable properties.

Turning now to FIGS. 19 to 22, the ferromagnetic coated conductor may beattached to a primary geometry. The primary geometry may provide anattachment surface or an internal site for the conductor with aferromagnetic coating. Thus the advantages of the ferromagnetic coatingon a conductor may be combined with the advantages of the primarygeometry and its corresponding material. The primary geometry may beselected for various reasons, including but not limited to, materialstrength, rigidity, heat conduction, resistance to thermal heattransfer, surface area, or additional functionality.

As used herein, a primary geometry means a structure to which aferromagnetic coated conductor may be attached and which defines theshape of the tool. For example, a primary geometry could be a scalpel,tines of forceps, the face of a spatula, or a ball shape at the end of aprobe. The conductor geometry, therefore, may be disposed upon theprimary geometry, may extend through a hole in the primary geometry,and/or be embedded in the primary geometry. For example, a primarygeometry may be a scalpel, while the conductor geometry may be theserpentine shape of a ferromagnetic coated wire upon the primarygeometry.

Turning now to FIGS. 19A and 19B, a cold cutting scalpel 223 withalternate inductive ferromagnetic thermal function is shown. The coldcutting scalpel 223 may be used for cutting through the application of ablade having a cutting edge and having a secondary thermal functionactivated when required, such as for coagulation. In the embodimentsshown in FIGS. 19A and 19B, this is achieved by placing a ferromagneticcoated wire conductor 220 upon the side of a scalpel shaped primarygeometry, which can cut tissue without activation of the conductor orferromagnetic coating 65. The cold cutting scalpel 223 may be usedclassically to make incisions in tissue. However, if the patient beginsto bleed, the cold cutting scalpel 223 operator may activate theferromagnetic coated conductor and place the side of the cold cuttingscalpel 223 (and correspondingly, the ferromagnetic coated conductor)upon the bleeding tissue. The thermal effect may then cause the tissueto seal and cease bleeding. After deactivation of the ferromagneticcoated conductor, the scalpel operator may then return to makingincisions with the benefits of a cold cutting scalpel.

There are several advantages to use of such a cold cutting scalpel 223.The dual-use tool does not require the cold cutting scalpel 223 operatorto remove one tool and replace it with another, causing risk of furtherdamage and delay. Due to the ferromagnetic coating 65, the cold cuttingscalpel 223 may also have a quick thermal response time (the heat-up andcool-down time) in the region of the ferromagnetic coating 65 such thatthe cold cutting scalpel 223 may be used on the targeted area and reducewaiting time. In cases where it may be desirable to heat the entire coldcutting scalpel, thermal response time may be further reduced byremoving a center portion 222 of the blade (as seen in FIG. 19B),resulting in a non-contiguous portion of the blade that may occurbetween or adjacent to the conductor path. Removing the center portion222 of the blade may further reduce the thermal mass and correspondinglythe thermal response time.

In one embodiment, related to FIG. 19B, the ferromagnetic coating may belimited to a part of the scalpel, such as the tip of the cold cuttingscalpel 223. This limiting would cause only the tip to heat, while theremaining portions of the primary geometry would remain at a lowertemperature. This limiting of the heating to a portion of the primarygeometry in proximity to the ferromagnetic coating may provide a higherdegree of accuracy and usefulness in smaller spaces. Similarly, theferromagnetic coated wire conductor 220 may form a pattern, such as azigzag or serpentine pattern, across the surface of the cold cuttingscalpel 223 to increase the heating coverage of the surface.

Scalpel effects may also be enhanced by the thermal effects of theferromagnetic coated wire conductor 220. In one embodiment, the scalpelmay have multiple parts with different temperature ranges addressable toeach part. For example, energy to the scalpel blade may be used to cut,while energy to the sides of the blade may be used to coagulate tissuewalls. In another embodiment, the ferromagnetic coated wire conductor220 may be activated to provide additional cutting ability when movingthrough more difficult tissue. In another embodiment, the ferromagneticcoated conductor may be activated to provide a more smooth cuttingprocess in conjunction with the scalpel blade. A user control may beused to select a power setting to be delivered by a power source, whichmay be correlated with a desired temperature or tissue effect.

Turning now to FIG. 20A, a thermal surgical tool with a spatula shapedgeometry is shown. The spatula 224 may have a ferromagnetic coating 65on a wire conductor 220 that follows the perimeter of the spatula shapeas shown. In an alternate embodiment, the ferromagnetic coated portionof the wire conductor 220 may form a pattern across the surface of thegeometry such that the surface is more evenly covered by theferromagnetic coated portion of the wire conductor 220.

A spatula geometry may be useful for various tissue effects andprocedures. In one embodiment, the spatula is used for hemostasis ortissue welding during surgery. After an incision has been made, ifneeded, the spatula may be applied to the incised tissue to achievehemostasis or even tissue welding. In another embodiment, the spatulapressed into tissue and thermal energy is used for tissue ablation.

Turning now to FIG. 20B, the thermal surgical tool with a spatula shapedgeometry is shown in forceps form. The spatula forceps 225 may be usedin combination such that each spatula has a separate power control orthe forceps may have a power control in common. Such a tool can be usedto clamp vessels to stop blood flow, and then cause hemostasis andcutting of the vessels with heat.

Turning now to FIGS. 20C and 20D, a side view of FIG. 20A is shown intwo different embodiments. The ferromagnetic coating and wire conductormay be attached to the primary geometry in several ways. In oneembodiment shown in 20C, the ferromagnetic coating 65 and conductor maybe attached to the surface of the primary geometry. Alternatively in20D, the ferromagnetic coating 65 and conductor may be embedded withinthe primary geometry. Depending upon the desired effect, the toolsdepicted in FIGS. 20A, 20B, 20C and 20D can be applied to tissue in sucha manner that the side of the tool on which the ferromagnetic coatedconductor 65 is located can contact the tissue, or the opposite side canbe applied to the tissue.

Turning now to FIGS. 21A, 21B and 21C, a thermal surgical tool with aball shaped geometry is shown. In one embodiment, a horizontally wrappedball 226 or a vertically wrapped ball 231 may be internally orexternally wrapped with a wire conductor 220 with a ferromagneticcoating 65 as seen in FIGS. 21A and FIG. 21C. In another embodiment,shown in FIG. 21B, a ball geometry 227 may contain a wire conductor 220with a ferromagnetic coating prepared in another shape, such as ahorseshoe shape. In the embodiments, a ball-shaped heating element maybe formed which can be used to coagulate or provide a therapeutic effectover a large surface area of tissue. The ball may also be effective intissue ablation, as it may radiate thermal energy in most, if not all,directions.

Turning now to FIG. 22A, a thermal surgical tool with a pointed geometryis shown. The pointed tool 228 may have a ferromagnetic coating 65 on awire conductor 220 that follows the perimeter of the pointed tool shapeas shown. In an alternate embodiment, the ferromagnetic coated portionof the wire conductor 220 may form a pattern across the point surface ofthe geometry such that the point surface is more evenly covered by theferromagnetic coated portion of the wire conductor 220. The pointed tool228 may be particularly useful for making incisions that penetratelayers of tissue, providing a means for coagulation while cutting, suchas coagulation of tissue around the site of trocar insertion forlaparoscopic surgery.

Turning now to FIG. 22B, the thermal surgical tool with a pointedgeometry is shown in forceps form. The pointed forceps 229 may be usedin combination such that each pointed geometry has a separate powercontrol or the forceps may have a power control in common. Such a toolcan be configured for achieving hemostasis and cutting in small vesselligation.

While some primary geometries have been shown in singular form, theprimary geometries may be used in combination. This may include two ormore of the same primary geometry or differing primary geometries,including forceps applications. Each primary geometry may be commonlycontrolled for power or have separate power controls for each primarygeometry. Furthermore, solid primary geometries may be altered similarto the scalpel primary geometry shown above such that portions of theprimary geometries may be removed to reduce thermal mass andcorrespondingly, thermal response time.

While some of the primary geometries have been shown to have symmetricalconstruction, the primary geometries may have asymmetrical ordirectional construction such that only a portion of the primarygeometry would be active. This may be accomplished by placing theferromagnetic coating only on the portion of conductor wire residing onthe area of the primary geometry desired to be active. For example, thespatula geometry may be configured to be active in one area if theferromagnetic coated conductor is not symmetrically positioned on thespatula structure. This may be further enhanced by providing a pattern,such as a zigzag or serpentine pattern, on the desired active portion ofthe geometry.

In another embodiment, a portion of the primary geometry may beactivated. By using multiple conductors with a ferromagnetic coating 65attached to different portions of a primary geometry, a portion of theprimary geometry may be selectively activated. For example, a scalpelgeometry 232 may be divided into a tip portion 234 and a face portion236 as shown in FIG. 22C. A scalpel operator may then choose whether toactivate only the tip or the tip in conjunction with the face of thescalpel geometry, depending on the surface area desired. Similarly, in aforceps application, the forceps may be divided into inside and outsideportions. If the forceps operator desires to remove something that maybe surrounded by the forceps, such as a polyp, the internal portions maybe activated while the external portions remain deactivated. If opposingsides of a void need to be sealed, the outside surfaces of the forcepsmay be activated.

By using multiple conductors with a ferromagnetic coating 65 attached todifferent portions of a primary geometry and separately controlled powersources, different portions of the primary geometry may be activated atthe same time for different uses or effects. For example, an edgeportion of a primary geometry may be activated for cutting while theblade portion may be activated for hemostasis.

A method of treating tissue may thus include the steps of: selecting aprimary geometry having a conductor disposed thereon, the conductorhaving a ferromagnetic coating disposed on a portion thereof; disposingthe ferromagnetic coating into contact with the tissue; and deliveringan oscillating electrical signal to the conductor so as to heat theferromagnetic coating and treat the tissue.

Optional steps of the method may include choosing a primary geometryselected from the group of scalpel, spatula, ball and pointed geometry.Treating of the tissue may include incising, causing hemostasis,ablating or vascular endothelial welding.

A method for tissue destruction may include the steps of selecting aconductor having a ferromagnetic coating disposed on a portion thereof;and delivering an oscillating electrical signal to the conductor so asto heat the ferromagnetic coating and destroy tissue.

Optional steps of the method may include monitoring the tissue andceasing delivery of the oscillating electrical signal to the conductorwhen the desired tissue destruction has occurred or undesired tissueeffects are to be prevented.

A method for forming a surgical instrument may include the steps of:selecting a primary geometry; coating a conductor with ferromagneticmaterial; and disposing the conductor on the primary geometry.

Optional steps of the method may include providing electricalconnections on the conductor configured for receiving oscillatingelectrical energy.

Turning now to FIG. 23A, a catheter 270 having a conductor 220 which isat least partially coated with ferromagnetic material disposed aroundthe tip of the catheter is shown. Depending upon the therapeutic effectdesired, the location of the coil of ferromagnetic coating 65 couldinstead be inside the catheter tip, or a single loop of ferromagneticcoated conductor having a circumference which approximates that of thecatheter central channel 260 could be located at the end of the cathetertip.

In FIG. 23B, another ferromagnetic coated catheter 270 is shown. Whilein some embodiments the conductor may be a wire, coil, or annularstructure, a ferromagnetic coated catheter 270 could also be formedwhich would serve as an alternate conductor 250 with a ferromagneticcoating 65. In this embodiment, the catheter could consist of twocoaxial conductors, separated by an insulator. At the distal tip of thecatheter 270, a conductive coating can be applied such that a continuouselectrical path is created by the coaxial conductors. The ferromagneticcoating can be dispersed about the external diameter surface near thedistal tip of the catheter, as shown in FIG. 23B, or, upon the end ofthe catheter, on the annular surface connecting the coaxial conductors.This would allow the ferromagnetic coated catheter 270 to perform otherfunctions, such as irrigation, aspiration, sensing, or, to allow viewingaccess via optical fibers, through a central channel 260, as is commonin many interventional as well as open and minimally invasive surgicalprocedures. Furthermore, the central lumen of the catheter could be usedto provide access to other sensing modalities, including, but notlimited to, impedance and pH.

It will be appreciated that the catheter 270 or an endoscope could beprovided with both a bipolar electrode and/or a thermal element. Thus,the benefits of such a catheter or endoscope could be combined with themulti-mode surgical tool discussed herein.

Turning now to FIG. 24, a side view of an alternate embodiment of aferromagnetic coated conductor surgical tool catheter tip 288 is shown.In one embodiment, the conductor may consist of a ferromagnetic coatedconductor positioned on a substrate 285 forming a body with a centralchannel. The ferromagnetic coating may consist of a plated ferromagneticcoating 275 on top of a conductor 289. The plating may be placed on theoutside of the substrate 285 such that the thermal effects are directedexternally. This may allow the catheter tip to apply thermal tissueeffects to tissue walls.

In another embodiment, the inside of the substrate may contain theconductor 289 and ferromagnetic coating 275 such that the thermaleffects are directed internally. An internal coating may allow deliveryof a meltable solid to a desired area, such as in fallopian tube sealingand osteosynthesis applications.

Alternatively, the ferromagnetic coating 275 may surround the entranceto the central channel 260, such that the thermal effects may bedirected in front of the tip. Having the thermal energy be directed infront of the central channel 260 entrance may aid in taking a tissuesample or removal of material, such as a polyp.

The plating may be accomplished through multiple methods. The substrate285 may be extruded, molded or formed from various materials includinghigh temperature thermoplastic, glass, or other suitable substratematerial. The actual plating may be accomplished through electroplating,electroless plating, vapor deposition, or etching, or some combinationthereof. Thus through the plating process, a catheter tip 288 may beformed with a ferromagnetic coating 275 on a conductor 280 with acontinuous path.

The catheter may also have multiple channels. One channel may be adeployment channel for the ferromagnetic coated conductor. Anotherchannel may be used for one or more sensors or sources, or even eachsensor or source in its own channel—such as a temperature sensor,illumination source and endoscope. Other channels may include delivery,irrigation or aspiration of substances, including those associated withtreatment, such as in osteosynthesis or fallopian tube sealing. In fact,the ferromagnetic coating may aid in the melting of such substances.

Turning now to FIG. 25, an endoscope 240 with a viewing channel 262 ofrod lens type or organized fiber bundle type aside a light emittingsource 266 is shown. A loop coagulator/cutter 264 is shown whichconsists of the ferromagnetic coated conductor 65. Such an adaptation iscontemplated in snare applications such as colon polypectomy or sealingand cutting applications in various laparoscopic procedures. Othersensing modalities include near field tumor cell detection or infraredheat monitoring. Tool configurations similar to the described endoscope240 can be embodied in tools that can be delivered to target tissuethrough the lumen of a catheter.

In one embodiment, tumor cells are caused to be tagged with materialsthat fluoresce when exposed to ultra-violet light. The endoscope 240 maycontain a light source 266, and sensor or optics within the channel 262that return the detected florescence. The ferromagnetic coating 65portion of the endoscope 240 may then be directed at the tagged tissuefor destruction.

In another embodiment, materials are deposited around target tissue orbone in a solidified condition. Once delivered, the materials are meltedto conformation at the site by activation by the endoscope 240 describedabove. Examples of use of this embodiment include fallopian tube sealingand osteosynthesis. Furthermore, such materials could be removed bymelting with the same or similar endoscope 240, and aspirated through acentral lumen of the endoscope 240. In yet further applications,materials may be delivered in liquid form, and cured by a thermalheating process induced by the endoscope 240.

Alternatively, the conductor may be part of a bundle of fibers. Thefibers may be contained within a catheter or otherwise bundled together.The conductor may have a ferromagnetic coating, while the other fibersmay have other purposes that include visual observation, sensing,aspiration, or irrigation.

A method of tissue ablation may include the steps of: selecting acatheter with a ferromagnetic covered conductor; causing theferromagnetic covered conductor to touch tissue to be ablated; anddelivering power to the ferromagnetic covered conductor.

Optional steps may include: directing the catheter to the tissue throughthe aid of an endoscope; selecting a ferromagnetic coated conductordisposed on the catheter; selecting a ferromagnetic coated conductorcontained within the catheter; causing the ferromagnetic coatedconductor to be deployed from the catheter; or touching theferromagnetic coated conductor to the tissue to be ablated.

A method of delivering a substance into a body may include the steps of:selecting a catheter with a ferromagnetic coated conductor; placing asubstance in the catheter; inserting the catheter into a body; andcausing power to be sent to the ferromagnetic coated conductor.

Optional steps may include: selecting a substance for osteosynthesis;selecting a substance for fallopian tube sealing; or melting thesubstance in the catheter.

A method of treating tissue may include the steps of: selecting acatheter with a ferromagnetic coated conductor; placing the catheter incontact with tissue; and selecting a power setting. The temperaturerange may correspond to a temperature range or desired tissue effect.The desired tissue effect may be selected from the group of vascularendothelial welding, hemostasis, searing, sealing, incision, ablation,or vaporization. In fact, the power setting may correspond to a desiredtissue effect.

Turning now to FIG. 26, a tissue ablation tool 290 is shown. In typicalapplications of tissue ablation, an arm or tine 295 is inserted intoundesired tissue. One or more tips 300 may be activated such that thetissue temperature is raised to a desired level for a desired amount oftime. After the activation has succeed in holding a temperature for adesired amount of time, or undesired effects are noticed, the one ormore tips 300 may be deactivated and removed from the tissue.

In one embodiment, a conductor may be contained in one or more arms ortines 295 with tips 300 that may contain ferromagnetic coatings 65. Thetips 300 may be inserted into tissue and temperature controlled untiltissue destruction occurs or one or more undesired tissue effects occur.The tissue effects may be monitored through sensors in the tines 295 orexternally.

Sensors may be placed in multiple ways. In one embodiment, the sensor isplaced in the tine and away from a ferromagnetic coated tip 300. Inanother embodiment, one tip 300 may have a ferromagnetic coating, whilean alternate tip 300 may have no coating, but a sensor contained within.The sensors may monitor tissue effects or return signals to be observedor processed. This may include sensors such as temperature sensors,cameras and remote imaging. In another embodiment, the temperature maybe monitored through external imaging.

The sensor may thus form part of a feedback loop. By monitoring one ormore tissue effects, the ablation tool may self-adjust power settings.This self-adjustment may allow the system to operate below the Curiepoint and still maintain a desired tissue effect and/or temperaturerange.

In the case where more than one tip 300 is used, the tips 300 with aferromagnetic coating 65 may be individually controlled such that thethermal profile is concentrated in the desired area. This may also allowa second tine to monitor tissue effects, while a primary tine is used toperform the thermal function.

While a diagram has been shown of a multi-tip tissue ablation tool inFIG. 26, a single tissue ablation tool may be made in a configurationsimilar to FIG. 7C.

Besides the advantages of uses in tissue, the surgical tool may also beself-cleaning. In one embodiment, when activated in air, the tool mayachieve a temperature sufficient to carbonize or vaporize tissue debris.

While the above embodiments have disclosed a ferromagnetic conductoroperating solely in an inductive heating modality, in accordance withthe principles of the present invention, a thermal surgical system maybe combined with other technology to form multi-mode surgicalinstruments. The multi-mode surgical instruments may leverage theadvantages of multiple energy modalities, while potentially reducingsome inherent drawbacks of either modality by itself. (While a fewexamples are discussed, it will be appreciated that a multi-modesurgical modality can be accomplished by modifying virtually any of theembodiments discussed above).

As used herein, multiplex means communicating the two or more signalsover a single channel. In many cases, the channel may be a wire orcable, and the signals may be imposed independently, or simultaneously,over the single channel.

Different modalities may be combined. Thermal modalities may be formedfrom thermal elements that produce thermal energy and include, but arenot limited to, inductive heating, conductive heating and resistiveheating devices. Electrosurgery modalities may be formed fromelectrosurgical elements that transmit electrical energy into the targettissue and include, but are not limited to, monopolar and bipolarmodalities. Mechanical modalities may be formed from ultrasonic elementsthat transmit mechanical energy in the form of pressure waves (alsoknown as ultrasonic energy) into the target tissue and include, but arenot limited to ultrasound tissue disruption. These modalities may havedifferent advantages in combination.

Inductive heating may be the result of a substance's resistance tomagnetic or electrical forces. Inductive heating may include sucheffects as the ferromagnetic effect, as described above, or aferroelectric effect in which substances may resist changes in electricfields.

As used herein, “conductive heating” or “conductive heating element”refer to the transfer of thermal energy from a heat source to anendpoint through one or more intervening elements. For example, asurgical tool may use thermal heat transfer to cause thermal energy tobe transferred from a heat source, such as a ferromagnetic inductiveheater, through an intervening element, such as a wire, to a surgicaltip, the endpoint. The process of conductive heating may be similar tothe heat sinks described above; only the thermal transfer is directed tothe tissue rather than another medium. See also the description of heatsinks relative to FIG. 4A.

Resistive heating may also be used as a thermal modality. A resistanceheating element may resist the passage of electrical current and thusdissipate power in the form of thermal energy.

In the monopolar surgery modality, a surgeon may use a single electrodeto pass electrical current through the body. Often, a second electrodeis attached to the back, legs or the surgical table to complete thecircuit. However, some monopolar devices also operate without a returnelectrode with low-powered high frequency current because of the body'sself-capacitance acting as a return path by the displacement current.

In the bipolar surgery modality, the electric current may be applied tothe patient through multiple electrodes. In one embodiment, the electriccurrent is applied through electrodes on opposite tines of forceps. Thetissue between the forceps may thus be heated.

In the ultrasound tissue disruption modality, ultrasonic vibrations areused to incise or destroy or ablate tissue in a region throughmechanical energy transfer. In one embodiment, a handpiece contains avibrating component or structure that mechanically transmits theultrasonic vibrations in tissues.

It is believed that these modalities may have advantages anddisadvantages when used as a sole modality. However, when multiplemodalities are used together, some disadvantages may be reduced andpotential advantages gained.

Turning now to FIG. 27, a multi-mode surgical tool 500 with monopolarand thermal modalities is shown. The multi-mode surgical tool 500 mayinclude a handpiece 505, a secondary electrode 510 and a power supply515. The power supply 515 may provide two signals to the handpiece 505to activate the thermal and monopolar modalities in a surgical tip 525.The monopolar modality may then pass current through tissue (typicallythe patient's body) to a secondary electrode.

In a multiplexed embodiment, the monopolar signal may be prevented fromusing the cable 530 as the return path by a filter 531. The filter mayprevent the monopolar signal from returning along the cable 530, butallow the thermal signal to return along the cable 530. While the filter531 is shown between the power supply 515 and the handpiece 505, it maybe integrated elsewhere along the signal path, including within thepower supply, within the handpiece or on the return path just after theferromagnetic coating.

The signal may be multiplexed in many different ways. The signal may begenerated by a specialized signal generator, multiplexed before theamplifier, multiplexed after an amplifier, or even multiplexed at thehandpiece.

The handpiece 505 may include a handle 520 and surgical tip 525. In someembodiments, there may be a cable 530 connection between the handpiece505 and the power supply 515. The handpiece may also contain controlsfor operating the surgical tip, such as a button 535.

The surgical tip may be constructed in several different ways. Onesurgical tip may accept a multiplexed signal. Another surgical tip mayrequire separate signal pathways and structures. Thus a surgical toolmay have a electrosurgical electrode, such as a monopolar electrode, anda thermal element as separate structures. These structures may betotally separate, adjacent or overlap.

In the multiplexed embodiment, the surgical tip may be constructed of asingle ferromagnetic coating upon a conductor. The ferromagnetic coatingreceives two waveforms corresponding to a monopolar modality and aninductive heating modality. The monopolar waveform is transmittedthrough the ferromagnetic coating to the patient, while the inductiveheating waveform (or signal) is converted to thermal energy at theferromagnetic coating. A filter may insure the transfer of the monopolarsignal to the tissue as it blocks the monopolar electrical signal returnpath. The monopolar waveform may be between 200 kHz and 2 MHz.Preferably, the monopolar signal may be between 350 kHz and 800 kHz. Theinductive heating waveform may be, for example, between 5 MHz to 24 GHz,and preferably between 40 MHz and 928 MHz.

In one embodiment, the monopolar signal is between 350 kHz and 800 kHz.The inductive heating waveform is in the 40.68 MHz ISM band. Thewaveforms are multiplexed by the power supply 515 and sent along thecable 530 to the handpiece 520. (Alternatively, other methods ofmultiplexing the waveforms may also be used, such as joining two wirescarrying signals after the power supply or other multiplexing methods).

The handpiece 520 connects the cable 530 to the surgical tip 525 whichmay be composed of a ferromagnetic coating on a conductor. Theferromagnetic coating converts the 40.68 MHz signal into thermal energy,while transmitting the 350 kHz to 800 kHz monopolar signal through thetissue and eventually to the secondary electrode 510.

The monopolar modality may maintain the advantages of cutting, while theinductive heating modality produces hemostasis and may reduce the forcerequired to draw the surgical tip through tissue. Thus, when in use, thesurgeon may use RF waveforms suited to cutting, while using the thermalcontact of the coated portion for sealing or hemostasis. Thus deeptissue effects associated with RF coagulation or fulguration waveformsor blended waveforms may be minimized while maintaining the benefit ofRF cutting. The combined instrument may also be configured with separateRF frequencies or current pathways to optimize both ferromagneticinductive heating and electrosurgical cutting.

In a separate signal pathway embodiment, the surgical tip 525 may becomposed of a monopolar electrode disposed upon a thermal structure. Theheat from the thermal structure, such as a ferromagnetic coatedconductor, may be transferred through the electrode to tissue. In someembodiments, the thermal structure will be separated from the monopolarelectrode by an electrically insulating, thermally conductive coating.The electrode and thermal structure may have individual electricalconnections such that the correct signal may be sent to each.

The electrode may also be disposed next to the thermal structure. In oneembodiment, the monopolar electrode is arranged such that the electrodeencounters the tissue first, thereby cutting or ablating tissue. Thetrailing thermal structure may then encounter the freshly cut or ablatedtissue and apply thermal hemostasis. Thus, it will be apparent that themodalities may be used completely independently, simultaneously on thesame tissue, or closely following one another depending on the surgicalinstruments configuration and the effects desired by the physician.

While the embodiments above discuss the multi-mode surgical tool 500 asusing a monopolar modality for cutting and a thermal modality forhemostasis, it should be recognized that either modality may be adaptedto other tissue effects, whether the same or different. For example, inone embodiment, the monopole electrode and the thermal element areactive at the same time. The monopolar electrode waveform and thethermal element waveform may both be optimized for incising. This maymake the incision through tissue easier and more effective. In anotherembodiment, the thermal structure may be used for incising and themonopolar electrode may be used for hemostasis.

The monopolar multi-mode device may use the functions of either modalityin tandem or separately. In fact, the oscillators may be separatelyadjusted. In an embodiment, a monopolar modality and thermal modalityare activated at different times. The monopolar modality is activated toincise tissue. If hemostasis is needed, the thermal portion may beactivated on demand, and may remain deactivated until required by thesurgeon.

The power supply 515 may control the modalities separately or in tandem.For instance, a press of button 535 may cause both modalities toactivate in tandem. Or, the button 535 may be configured to activate oneor both modalities. However, the power supply may also control the powerdelivery to each modality via separate controls 540, which may beseparately adjustable.

The multi-mode surgical tool may be disposed upon a catheter. Thecatheter may allow more functionality such as sensing, visual feedback,irrigation, aspiration, or substance delivery. In fact, the catheter maybe flexible or rigid depending on the desired application.

A process of using a thermally adjustable multi-mode surgical tool mayinclude the steps of: generating a first oscillating electrical signalforming an approximate standing wave with maximum current and minimumvoltage substantially at a first load disposed along a conductor whichhas a portion of the conductor coated by ferromagnetic material tocreate thermal effects in tissue; and generating a second oscillatingelectrical signal along a conductor to create electrosurgical tissueeffects in tissue.

The process may include the optional steps of: creating hemostasis inthe tissue; causing tissue cutting; generating the first oscillatingelectrical signal and the second oscillating electrical in a singleconductor; or generating the first oscillating electrical signal and thesecond oscillating electrical signal during overlapping periods of time.In fact the conductor may comprise a monopolar electrode.

A method for incising and sealing tissue may include the steps of:selecting a surgical tool, the tool having a conductor with aferromagnetic coating disposed on a portion thereof, the tool alsohaving an electrode; disposing the electrode in contact with tissue;disposing the ferromagnetic coating into contact with the tissue;delivering an oscillating electrical signal to the electrode so asincise the tissue; and delivering an oscillating electrical signal tothe conductor so as to heat the ferromagnetic coating and seal thetissue.

The method may include the optional steps of: heating the ferromagneticcoating to provide hemostasis and selecting a monopolar electrode.

Turning now to FIGS. 28A, 28B and 28C, a lesioning or ablating probe 420is shown. A lesioning probe may be placed within a lesion and heated toa specified temperature for a specified period of time. Generally, thedesire is to kill or ablate the lesion while leaving other tissueminimally effected. During this process, the progression of the heat ismonitored such that any unforeseen irregularities may cause theprocedure to abort rather than further damage the patient's tissues.This progression is known as the heat shape or shaping effect. Theferromagnetic coating may itself be biocompatible, or, if it is not, itmay have at least a portion covered in a second coating, such as abiocompatible material or non-stick material. In one embodiment, aferromagnetic inductive tip 422 may be covered by a coating of gold(sometimes referred to as a cap). The tip coating of gold may bebiocompatible, yet highly heat conductive and therefore practical for amore slow temporal heating and shaping effect. Although gold may beused, other biocompatible materials, such as silver, may be used aswell. A conductive coating may aid in the transmission of monopolarenergy, if covering the monopolar electrode.

The probe 420 may operate through the use of more than one modality. Inone embodiment, an electrode may be optimized for incising for insertioninto the tissue, while a thermal element is optimized for tissueablation. Both the electrode and the thermal element may be contained inor near the tip 422. Thus the electrosurgical element may allowinsertion of the instrument into the desired tissue, while the thermalportion may be used for ablation. Similarly, the tool may also beconfigured for RF tissue ablation and thermal incision.

In one embodiment of a method of using the probe 420, the probe 420 maybe guided stereotactically into a tissue to selectively lesion afunctional path. Common examples include functional stereotactic brainlesioning in the treatment of movement disorders, pain, and depression.One advantage compared against commonly employed single modalitymonopolar and single modality bipolar probe configurations is that theshape of the lesion may be controlled by the thermal conductionproperties and/or electrical impedance properties, giving the clinicianbetter ability to adjust the shaping effect in the tissue.Alternatively, ablation for intended gradual heat destruction of atissue can be achieved with similar designs, typically employing highertemperatures. Such an embodiment is easily adapted for treatment oftumor metastases in various organs. Another advantage of the multiplemodalities may be giving the ability to target tissue where theelectrical and thermal effects overlap, rather than choosing a lessperfect targeting of a single modality.

As illustrated in FIG. 28A, the lesioning or ablating probe 420 may bepositioned into a metastasis 424 in tissue, e.g. an organ such as theliver 426. Once in the liver, etc., one or both modalities may cause themetastasis 424 to heat to a desired temperature for a desired period oftime. Thermal modalities may cause the tip 422 to heat. The shape of thetemperature envelope may be examined by temperature sensing and orexternal means such as ultrasound. Similarly, the electrical effect ofan electrical modality may be measured as well, such as impedancemeasurements. After the elapsed time, the probe 420 may be removed fromthe lesion. Thus, the undesired tissue of the tumor may be killed whileminimizing harm to the surrounding tissues. Distributed tissue ablativeeffects can be optimized by cross-sectional monitoring of the electricalimpedance changes in tissue, as illustrated in bronchial thermoplasty,prostatic hypertrophy, and volumetric reduction (lesioning).

Turning now to FIG. 28B, a close-up of the ablating probe of FIG. 28A isshown. The probe may have an elongate body 421 that ends in a multi-modetip 420, such as a ferromagnetic coated conductor 423. The multi-modetip 420 may include a sensor 425 as seen in FIG. 28C. In one embodimentas shown in FIG. 28D, the ablating probe may include a first multi-modetip 420 and a second tip 427. In one embodiment, the first tip mayinclude the multi-mode functionality and the second tip 427 may containa sensor. In another embodiment, the first and second tip (also known asa primary tip and secondary tip) may contain multi-mode tips.

A method of tissue ablation may include the steps of: selecting a tipwith electrosurgical and thermal modalities; inserting the tip into theundesired tissue; and activating one or more of the modalities withinthe undesired tissue.

A method for treating tissue may include the steps of: selecting asurgical handpiece and delivering thermal energy at, at least, 58degrees Celsius to the tissue from the handpiece and deliveringelectrical energy from the handpiece to the tissue to thereby treat thetissue.

It should be recognized that multi-mode surgical tips with aferromagnetic coating may have a relevant Curie point large enough toencompass a desired set of therapeutic temperature ranges withoutcrossing the Curie point.

Turning now to FIG. 29, a multi-mode surgical tool 550 with bipolar andthermal modalities is shown. The power supply 515 may supply bipolar andthermal signals through a cable 530 to multi-mode forceps 555. Thebipolar signal may be transferred through a first forceps tip 560through tissue into a second forceps tip 560 using a bipolar waveform.The thermal signal may be converted into thermal energy by heatingelements within one or more of the forceps tips 560.

The multi-mode forceps combine thermal heating and bipolarelectrosurgery modalities into a multi-mode forceps tip 560. The forcepstip 560 may allow for cutting using an electrosurgical element, andsealing with the thermal portion to thereby provide improved cutting andsealing of the tissue. The surgical tool may also allow for other tissueeffects to be applied to tissue either by both modalities in tandem oras needed. In other words, the electrosurgical modality and the thermalmodality may be used at different times or may overlap. For example, aphysician may contact tissue with the bipolar element to incise thetissue until he or she encounters undesired bleeding, at which time heor she can dispose the thermal element adjacent the bleeding tissue andactivate the thermal modality for hemostasis. This can be done afterstopping the bipolar modality, or while the bipolar modality is stillbeing used (e.g. closely following the bipolar modality as the physicianincises tissue. Controls 540 can be provided to prevent both being usedsimultaneously or overlapping, or the user can control when eachmodality is used.

Similarly, the surgical tool may also use both modalities to applysimilar tissue effects or different tissue effects. A control such as ahandpiece control 561 may be provided to allow the physician toselectively use the bipolar modality, the thermal modality or both.

As in the monopolar multiplexed environment, the bipolar signal may beprevented from using the electrical return path of the thermal elementby a filter 533. Instead, the electrosurgical signal may be directedthrough tissue to access the return path.

Turning now to FIG. 30, a side view of a multi-mode forceps 400 isshown. In one embodiment, a nickel-iron alloy is used for ferromagneticinductive heating and electrosurgery modalities. The nickel-iron alloypasses low temperature cutting current waveforms into the tissue itself,while absorbing high frequency energy for inductive heating. Lowtemperature cutting current may have very little hemostatic property,but is also minimally injurious. Thus, low temperature cutting currentis a desirable cutting modality. To remedy the lack of hemostaticproperty, contact thermal sealing by the ferromagnetic coating avoidsthe deep contact desiccation and disruption effect of coagulation orfulguration waveforms as may be used in electrosurgery. Thus, theaddition of a ferromagnetic sealing element provides improved cuttingand sealing.

Various adaptations to the multi-mode forceps may be used to achievedesired effects. The combined instrument may multiplex RF frequencies oruse separate current pathways 404 to optimize both thermal andelectrosurgical modalities. Various tip geometries may be developed forsuch a hybrid instrument, including coapting bipolar forceps clad at thetips with thin magnetic film. The tip may have a coating 402 or partialcoating to aid in conduction of the signal or reducing the amount ofcoagulum buildup. The RF energy transfer may also be enhanced throughthe addition of conductive material during surgery, such as the additionof saline solution.

Turning now to FIG. 31A, close up of an alternate embodiment of forcepstips 410 is shown. In one embodiment, hemostatic forceps incorporate aferromagnetic heat source 412 on a first forceps tine 414 and a thermalsensor in an opposite tine 414′. The feedback of the thermal sensor maybe reported such that an optimal tissue effect is reached andmaintained. The temperature may thus be regulated and power deliveryadjusted to provide the desired effect.

Adding a bipolar modality to the forceps tips 410 may improve thesingular thermal modality. The sensor may continue to report temperatureat the tines 414 or 414′, but its output may be used to make decisionson adjustments to both modalities.

Similar to the monopolar-thermal hybrid device, a bipolar-thermal devicemay contain bipolar electrodes and a thermal element. The bipolarmodality and thermal modality may be used together or independently, asneeded. Thus, the surgeon may select from the benefits of multiplemodalities. For example, to avoid deep tissue effects, the surgeon mayavoid blended bipolar waveforms related to hemostasis, but instead usethe integrated thermal modality of the forceps for hemostasis. Inanother embodiment, the surgeon may use the thermal modality forincising soft tissue, but may select to add the bipolar modality with acutting waveform when more resistant tissue is reached.

A sensor may be placed within a multi-mode device to detect temperatureor tissue effects. The information from the sensor may then be used toadjust the output of the multi-mode device. In one embodiment, thesensor may detect tissue charring. The generator may then be notified toscale back the power delivered to the bipolar or thermal system that mayhave caused the charring.

Turning now to FIG. 31B, a diagram of a coated forceps tine 414 isshown. In one embodiment a non-stick covering 416 over the ferromagneticcoating, such as Teflon, may markedly decrease coagulum build-up and thenecessity for instrument cleaning. However haphazard application of thecoating may also impede the dynamics of rapid temperature acquisitionand rapid decay due to its thermal conduction properties. By selectingthe coating material by important characteristics, including thermalmass and thickness, desired temperature retention characteristics may beachieved. Furthermore, a non-conductive coating may only be partial,thus reducing the electrosurgical resistance, but keeping the benefit ofa non-conductive coating like Teflon.

The bipolar multi-mode surgical tool may also be disposed upon acatheter. The catheter may be rigid or flexible. The catheter may alsobe configured for aspiration, irrigation, substance delivery, visualfeedback, sensing with a senor, or other applications.

A method of treating tissue may include the steps of: selecting asurgical tool with electrosurgical and thermal modalities; disposing atip in contact with tissue; and activating at least one of themodalities.

The method may optionally include the steps of: selecting a desiredtemperature range; selecting a bipolar modality; selecting a powersetting corresponding to a desired tissue effect; selecting a thermalmodality with a ferromagnetic coated conductor; activating a firstmodality for incising; activating a second modality for at least one ofvascular endothelial welding and hemostasis; activating the modalitiessuch that the modalities active period overlaps; or comprises activatingthe modalities such that the modalities active period is prevented fromoverlapping.

A method of incising tissue may include the steps of: selecting asurgical tool with bipolar and inductive heating modalities; activatingthe bipolar modality for incising; disposing the tip adjacent contactwith tissue; and activating the inductive heating modality for at leastone of vascular endothelial welding and hemostasis.

The method may optionally include the steps of: comprises maintainingthe bipolar modality active while activating the heating modality tothereby incise tissue and create hemostasis at substantially the sametime; or using a surgical instrument having a pair of arms with abipolar electrode and a thermal element on the same arm.

Turning now to FIG. 32A, a multi-mode surgical tool 430 with thermal andultrasonic modalities is shown. Power is provided to an ultrasonictransducer 431 (which drives a load) to create ultrasonic motion, asshown by arrows 432, of a body 434 that may include an ultrasonic horn435. During operation, the body 434 may disrupt tissue with theultrasonic energy, i.e. can incise or help break up undesired tissue.Alternatively, the ferromagnetic coated conductor can be actuated by lowfrequency mechanical vibrational energy.

As the tissue is disrupted by ultrasonic (or vibrational) energy, athermal element, such as a coated ferromagnetic wire or ferromagneticcoated conductor 436, at the tip of the body 434 may be heated toachieve a desired thermal effect, such as hemostasis. (The ferromagneticcoating acts as a load for a waveform as discussed above).

While the above diagram is shown to operate linearly, other geometricalmotions may be used. For example, in one embodiment, the body oscillatesin a circular motion. The rotation may be centered around the axis shownby arrows 432. In another embodiment, the body may oscillate in both theaxis direction of arrows 432 and circularly around the axis shown byarrows 432.

In use, a power source provides inductive heating signals, i.e.waveforms as discussed above, to the conductor 436 to provide a thermalmodality. At the same time and/or independently, a ultrasonic signal,i.e. a signal which drives an ultrasonic transducer 433 or stack ofultrasonic transducers (433 and 433′), such as piezoelectrictransducers, are provided to move the body to create ultrasonicmovement. Thus, the body 434 can provide ultrasonic treatment before,during or after thermal treatment is being applied.

The tool may be used for incising, hemostasis, vascular endothelialwelding, tissue ablation or a combination thereof. In one embodiment,the ultrasonic modality may be used to incise, while the thermalmodality may be used for hemostasis. In another embodiment, theultrasonic modality is used to insert a tip into tissue and the thermalmodality is used for tissue ablation.

Turning now to FIG. 32B, an multi-mode surgical tool with thermal andultrasonic modalities and a hook primary geometry 437 is shown. Themulti-mode tool 430 may also include a primary geometry to which athermal element may be attached. Similarly, the thermal element may beconfigured for a various tissue effects.

Turning now to FIG. 32C, a sensor 439 has been added to FIG. 32A. Thesensor may detect tissue effects or even the temperature of the device,similar to other sensors already discussed. Similarly, the sensor may beused as a feedback mechanism in the control of the available modalities,including the power delivery.

Turning now to FIG. 32D, a second tip 441 may be placed in proximity tothe first tip 436. The second tip may also contain one or more sensorsor another modality, including a multi-mode tip.

Turning now to FIG. 33, a multi-mode surgical tool 569 with thermal andultrasonic modalities and aspiration/irrigation is shown. The tool 569includes a power supply 515 with a plurality of controls 540 that may beindividually addressable for providing energy and controlling a pump (ifdesired) for irrigation or aspiration, to a handpiece 570 via a cable530. The handpiece 570 includes an oscillating body 580 and a thermalelement 585.

The power supply 515 may provide ultrasonic and thermal signals to driverespective loads (i.e. the body 580 and the thermal element 585). (Asimilar power supply could be used with the embodiment shown in FIG.32). The power supply 515 may provide individual or multiplexed signalsto the handpiece 570. Each signal may be individually controlled bycontrols 540, buttons 591 or in some cases, jointly controlled byactivation of the handpiece. In fact, the suction may also be controlledin the same manner—individually or jointly.

In addition to signals to create ultrasonic and thermal energy, thepower supply 515 may be configured to provide suction, for example,through a lumen or aspirating bore 590, through the grip 575 of thehandpiece 570 and through a tube/cable 530 to a reservoir. In theembodiment shown in FIG. 33, the reservoir may be contained in the powersupply 515.

The handpiece 570 may contain a grip 575, body 580 (which forms a lumen,bore or catheter) and surgical tip 585. In one embodiment, the grip 575contains an actuator or control 591 that causes ultrasonic vibration oftip of the body or catheter 580. The tip of the catheter 580 may includea heating element, such as a ferromagnetic coated conductor 585. As theultrasonic or thermal energy is applied to the tissue, the catheter bore590 may aspirate any disrupted tissue, including fat, or associatedeffects.

In one embodiment, the multi-mode surgical tool 569 may provide adelivery or irrigation mechanism. In one embodiment, a substance may beplaced in the catheter lumen 590. The ultrasonic mode may be used todisrupt enough tissue to arrive at a targeted delivery site for thesubstance to be deposited. At the targeted location, the thermal elementof the multi-mode surgical tool 569 may be activated such that thesubstance may melt and be deposited at the delivery site. If needed, thethermal element may be used for hemostasis or tissue welding during theinsertion or removal of the tool.

Similarly, the tool 569 may be used for delivery of other substancesthrough the catheter. While much of the discussion above centers onaspiration, the tool may be used to deliver substances through thecatheter. For instance, the tool 569 may be used to deliver salinesolution, medication, etc., including in a heated state if desired

In one embodiment, the catheter may have a plurality of bores. One boremay configured to aspirate, while another bore may be configured toirrigate.

Like the other embodiments discussed above, variety of sensors 593 maybe used. They could be disposed in the body 580 or could be insertedthrough the lumen 590. This could be accomplished via a port 592. Itwill be appreciated that the sensors could be temperature sensors,sensors which monitor tissue condition, devices for visualization, i.e.cameras, CCD sensors or fiber-optic wires, etc. Additionally, the powersource 515 could be made to react to the sensor, such as, for example,adjusting to keep heat in the thermal element 585 in a desired range forthe desired effect in the tissue, i.e. hemostasis, vascular welding,searing, incision or ablation.

A process of delivering power to a thermally adjustable multi-modesurgical tool may include the steps of: delivering a first oscillatingsignal to a conductor configured such that the first oscillatingelectrical signal forming an approximate standing wave with maximumcurrent and minimum voltage substantially at a first load comprising aportion of the conductor coated by ferromagnetic material; anddelivering a second oscillating signal to a second electrical connectionconfigured such that a second oscillating electrical signal will drivean ultrasonic transducer to thereby move a second load ultrasonically.

The process may include the optional steps of: placing the first loadadjacent tissue and wherein first oscillating electrical signal heats athermal element to a temperature causing hemostasis in the tissue andthe second oscillating electrical signal causes the second load toincise tissue; applying suction adjacent the first load and second loadto aspirate incised tissue; or multiplexing the first oscillating signaland the second oscillating signal in a communications channel to thefirst load and second load.

A method for incising and sealing tissue may include the steps of:selecting a surgical tool having a conductor with a ferromagneticcoating disposed on a portion thereof and an transducer which drives abody; disposing the body and ferromagnetic coating into contact with thetissue; delivering an oscillating electrical signal to the transducer soas incise the tissue; and delivering an oscillating electrical signal tothe conductor so as to heat the ferromagnetic coating and apply heat tothe tissue.

The method may also include the optional steps of: heating theferromagnetic coating to promote tissue hemostasis or selecting aultrasonic transducer.

A method for tissue ablation may include the steps of: selecting a tipwith ultrasonic and thermal modalities; inserting the tip into theundesired tissue; and activating one or more of the modalities withinthe undesired tissue.

The method may include the optional steps of: selecting a ferromagneticcoating as the thermal modality and aspirating residue from an areaproximate to the undesired tissue.

It will be appreciated that the various waveforms discussed for thethermal element may be used with each of the embodiments discussedherein. Additionally, it will be appreciated that aspects such sensorsand control responsive to sensors may be applied to each of theembodiments and are therefore not repeated in detail with respect toeach. Likewise, aspects of the thermal element, such as the use of anon-stick coating, and formation of the thermal element may be usedacross embodiments if desired.

Several advantages may be noted in use of embodiments of the presentinvention. In one embodiment, optimal thermal hemostatic effect inassociation with tissue ultrasound disruption and suction can beachieved for tumor debulkment as applied in solid organs, like thebrain. Alternatively, laparoscopic vascular dissection and detachmentcan be more optimally achieved compared to ultrasonic effects alone.

While a catheter has been discussed only with respect to the ultrasonicmodality, it should be noted that the catheter embodiment may be appliedto any of the multi-mode energy modalities and achieve each of thebenefits provided by the aspiration, sensors, etc. Similarly many of thebenefits of the ultrasonic and thermal multi-mode catheter embodimentmay be achieved with the other multi-mode embodiments. Those skilled inthe art will appreciate modifications to such embodiments to providethese multiple modalities of treatment.

Turning now to FIG. 34, a temperature spectrum is disclosed. Tissue mayreact differently at different temperatures and thus temperature rangeswill result in different treatments for tissue. Specific tissuetreatments are somewhat variable due to inconsistencies including tissuetype and patient differences. The following temperatures have been foundto be useful. Vascular endothelial welding may be optimal at 58-62degrees Centigrade. Tissue hemostasis without sticking may be optimallyachieved at 70-80 degrees Centigrade. At higher temperatures, tissuesearing and sealing may occur more quickly, but coagulum may build-up onthe instrument. Tissue incision may be achieved at 200 degreesCentigrade with some drag due to vaporization at the edges. Tissueablation and vaporization may occur rapidly in the 400-500 degreeCentigrade range. Thus, by controlling the temperature the “treatment”of tissue which the device delivers can be controlled, be it vascularendothelial welding, tissue incision, hemostasis or tissue ablation.

According to the spectrum disclosed above, power delivery settingscorresponding to the desired temperature range may be included in thepower delivery switch. In one embodiment, the foot pedal may haveseveral stops that indicate to the surgeon the likely tip temperaturerange of the current setting.

It will be appreciated that the thermal surgical tool system inaccordance with the present invention will have a wide variety of uses.Not only can it be used on humans, it can also be use to cut tissue ofother animals, such as in the context of a veterinarian or simplycutting tissues or biomaterials, such as those used for implantation,into smaller pieces for other uses.

Certain embodiments of the surgical system may have broad applicationwithin surgery as well. A loop geometry may have advantages in cutting,coagulation and biopsy applications. A blade geometry may haveadvantages for cutting and hemostasis applications. The point geometrymay have advantages in dissection and coagulation applications, and inparticular, neurodissection and coagulation. However, the application ofa geometry may be further configured and tailored to an application bydiameter, length, material characteristics and other characteristicsdiscussed above.

While the present invention has been described principally in the areaof surgical tools and the treatment of live tissue (though it can beused on dead tissue as well), it will be understood that a tool made inaccordance with the present invention and the methods discussed hereinmay have other uses. For example, a cutting tool could be formed forbutchering meat. Whether the meat is fresh or frozen, the tool can beuseful. For example, a cutting blade which is heated to a hightemperature will cut through frozen meat. However, when power is nolonger supplied, the “cutting” edge is safe to the touch. Likewise,cutting meat with a hemostasis setting would slightly sear the exteriorof the meat, locking in juices. Other uses of the instruments discussedherein will be understood by those skill in the art in light of thepresent description.

There is thus disclosed an improved multi-mode thermally adjustablesurgical tool. It will be appreciated that numerous changes may be madeto the present invention without departing from the scope of the claims.

1. A multi-mode adjustable surgical tool comprising: a body configuredto oscillate; a conductor placed around at least a portion of the body aferromagnetic coating covering a portion of the conductor; and a powersource delivering an oscillating current to the conductor.
 2. Themulti-mode surgical tool of claim 1, wherein the body comprises anultrasonic horn.
 3. The multi-mode surgical tool of claim 1, furthercomprising a power source for providing oscillating electrical energy tothereby oscillate the body and provide heating of the ferromagneticcoating.
 4. The multi-mode surgical tool of claim 3, wherein the powersource further comprises independent sources for providing energy tooscillate the body and for providing heating of the ferromagneticcoating.
 5. The multi-mode surgical tool of claim 4, wherein theindependent sources are configured to operate during overlapping periodsof time.
 6. The multi-mode surgical tool of claim 4, wherein theindependent sources are configured to operate during separate periods oftime.
 7. The multi-mode surgical tool of claim 1, wherein the body has abore.
 8. The multi-mode surgical tool of claim 7, wherein the body has aplurality of bores.
 9. The multi-mode surgical tool of claim 8, whereina first bore of the plurality of bores is configured to aspirate and asecond bore of the plurality of bores is configured to irrigate.
 10. Themulti-mode surgical tool of claim 1, wherein the power source furthercomprises power settings corresponding to desired tissue effects.
 11. Amulti-mode surgical tool comprising an ultrasonic transducer and athermal element.
 12. The multi-mode surgical tool of claim 11, whereinthe thermal element is a ferromagnetic coated conductor.
 13. Themulti-mode surgical tool of claim 12, wherein the ultrasonic transducerfurther comprises a piezoelectric transducer.
 14. The multi-modesurgical tool of claim 11, further comprising a power source forgenerating a multiplexed signal.
 15. The multi-mode surgical tool ofclaim 14, wherein the multiplexed signal comprises an ultrasonic signal.16. The multi-mode surgical tool of claim 15, wherein the multiplexedsignal comprises an inductive heating signal.
 17. The multi-modesurgical tool of claim 16, wherein the inductive heating signal isbetween 5 MHz and 24 GHz.
 18. The multi-mode surgical tool of claim 17,wherein the inductive heating signal is between 40 MHz and 928 MHz. 19.A multi-mode surgical tool comprising: a tip comprising: an electricalconductor; an ultrasonic transducer; and a ferromagnetic coatingcovering at least a portion of the electrical conductor.
 20. Themulti-mode surgical tool of claim 19, further comprising means forgenerating a multiplexed signal.
 21. The multi-mode surgical tool ofclaim 19, wherein the tip is part of an oscillating body.
 22. Themulti-mode surgical tool of claim 19, wherein the body comprises anaspirating bore.
 23. The multi-mode surgical tool of claim 21, whereinthe oscillating body further comprises an ultrasonic horn.
 24. Amulti-mode surgical tool comprising: a lesioning probe having: a tipcomprising and electrical conductor; a ferromagnetic coating covering aportion of the conductor; and an ultrasonic transducer.
 25. Themulti-mode surgical tool of claim 24, further comprising a power sourcedelivering an oscillating current to the tip.
 26. The multi-modesurgical tool of claim 25, further comprising a second tip, wherein thesecond tip comprises a sensor.
 27. The multi-mode surgical tool of claim26, wherein the power source is configured to react to the sensor. 28.The multi-mode surgical tool of claim 26, wherein the sensor isconfigured to measure temperature.
 29. The multi-mode surgical tool ofclaim 26, wherein the sensor is configured to measure transferred heat.30. The multi-mode surgical tool of claim 26, wherein the sensor isconfigured to measure tissue properties.
 31. The multi-mode surgicaltool of claim 26, wherein the sensor is configured to allow visualobservation of tissue.
 32. The multi-mode surgical tool of claim 25,wherein the power supply is configured to measure a temperatureindicator of the ferromagnetic coating and adjust an output to maintainpredetermined therapeutic temperature range in tissue.
 33. Themulti-mode surgical tool of claim 24, where the tip and conductor of thetool are coated with a thin layer of high temperature resistant,non-stick material.
 34. The multi-mode surgical tool of claim 24, wherethe tip of the tool is covered by a highly thermally conductive,biocompatible material.
 35. A multi-mode surgical catheter comprising: acatheter comprising; a surgical tip; a thermal element disposed on thesurgical tip; and an ultrasonic transducer configured to provideultrasonic energy to the surgical tip.
 36. The multi-mode catheter ofclaim 35, wherein the catheter further comprises at least one lumen. 37.The multi-mode catheter of claim 36, further comprises means fordeveloping suction within the lumen.
 38. The multi-mode catheter ofclaim 36, further comprising a substance disposed in the lumen fordelivery into a patient.
 39. The multi-mode catheter of claim 36,further comprising at least one sensor for sensing tissue condition. 40.The multi-mode catheter of claim 36, further comprising means forproviding visual feedback.
 41. A thermally adjustable multi-modesurgical tool comprising: a cable; a small diameter electrical conductorhaving a proximal and distal end, wherein the proximal end is configuredto receive radiofrequency energy from the cable; a thin plating offerromagnetic material disposed circumferentially about the electricalconductor, wherein the ferromagnetic material is configured with a Curiepoint sufficiently high to encompass a desired set of therapeutictemperature ranges; and an ultrasonic element connected configured toreceive power from the cable and configured to release ultrasonic energyinto nearby tissue.